Abstract:
An Apparatus for determining the disposition of an object relative to a reference frame includes at least one field generator, which generates an electromagnetic field in a vicinity of the object and at least one transducer, which is fixed to the object. The at least one transducer vibrates at a predetermined vibrational frequency and emits energy, responsive to an interaction of the electromagnetic field therewith. One or more detectors in a vicinity of the object are also utilized to detect the energy emitted by the transducer and generate signals in response thereto. A signal processor is also included for receiving and processing the detector signals to determine coordinates of the object.

Description:
FIELD OF THE INVENTION 
   The present invention relates generally to position sensing systems and specifically to systems for determining the position of an object inside a human body. 
   BACKGROUND OF THE INVENTION 
   In many medical procedures, probes, such as endoscopes and catheters, are inserted into a patient&#39;s body. Various methods of determining the location of these inserted medical devices are known in the art. X-ray imaging is the most commonly used location confirmation system. Position determining systems can also be used for this purpose. 
   Ultrasound intrabody position sensing is well known. Some such systems require an active transducer in the catheter, generally at or adjacent the distal end of the catheter, connected by wires to a console outside the body. The transducer either receives ultrasonic waves from emitters outside the body or radiates ultrasonic waves to receivers outside the body. Other ultrasonic systems use a passive ultrasound reflector in the catheter which gives a strong reflection of ultrasonic waves irradiating the body without the necessity of running wires through the catheter. These passive systems necessarily create a strong background of ultrasonic radiation against which the position of the reflector must be found. 
   U.S. Pat. No. 3,713,133 to Nathans, whose disclosure is incorporated herein by reference, describes a theft-prevention system in which a piezoelectric crystal having a resonant frequency is incorporated into a device which is then attached to individual items within a store. When a radio frequency (RF) signal having a frequency equal to the resonant frequency of the crystal strikes the crystal, an oscillating electrical field gradient is produced across the face of the crystal at the radiated RF frequency, and two tin foil members mounted on the crystal vibrate, emitting ultrasound. Detection of the ultrasound under appropriate conditions produces an alarm, indicative of an attempt to remove the item from the store without authorization. 
   U.S. Pat. No. 3,713,133 also describes a small, thin metal diaphragm having a resonant vibrational frequency. When the diaphragm is irradiated with an ultrasound field at or near the resonant frequency, the diaphragm vibrates at that frequency. An RF field also irradiates the diaphragm at a substantially higher frequency, and the vibration of the diaphragm induced by the ultrasound field modulates the RF field. This modulation is detected by an RF transducer, which activates an alarm. These systems do not provide specific information describing the location of the item, but only that the item has entered a detection area (typically near an exit from the store). 
   PCT Patent Publication WO 96/05768 to Ben-Haim et al., whose disclosure is incorporated herein by reference, describes a locating system for determining the location and orientation of an invasive medical instrument whereby an externally applied RF field induces a current in three coils located within the invasive medical instrument. Wires or some other form of physical leads are required to carry this induced signal from the catheter to a signal processor in the extrabody space. The processor analyzes the signal so as to calculate the location and orientation of the invasive medical instrument. 
   U.S. Pat. No. 5,522,869 to Burdette et al., and U.S. Pat. No. 5,549,638 to Burdette, whose disclosures are incorporated herein by reference, describe an ultrasound device for use in a thermotherapy apparatus to treat cancer. To operate this device, ultrasound transducers are arranged in a cylindrical shape around the treatment site, and are activated by radio frequency power. The resultant ultrasound waves heat tissue within the treatment site, thereby producing the desired therapeutic effect. The output of this device is therefore heat, and there is no indication of the location or orientation of the individual ultrasound transducers. 
   U.S. Pat. No. 5,325,873 to Hirschi et al., whose disclosure is incorporated herein by reference, describes a system to verify the location of a tube or other object inserted into the body. It incorporates a resonant electrical circuit attached to the object which resonates upon stimulation by a hand-held RF transmitter/receiver external to the body. The electromagnetic field generated due to resonance of the circuit is detected by the hand-held device, which subsequently turns on a series of LEDs to indicate to the user the direction to the target. An additional visual display indicates when the transmitter/receiver is directly above the object. 
   U.S. Pat. No. 5,412,619 to Bauer, whose disclosure is incorporated herein by reference, describes a system for tracking the three-dimensional position of a moving object. At least three ultrasound transmitters in known positions send signals which are detected by receiving stations mounted on the moving object. At each station, the detected signals are encoded into a form suitable for radio transmission, and a radio transmitter passes the information to a computer which determines the location of the object through a triangulation algorithm. The system in U.S. Pat. No. 5,412,619 is primarily suitable to be attached to the exterior of the human body to allow determination of gross body positions and movements. 
   U.S. Pat. No. 4,807,202 to Cherri et al, whose disclosure is incorporated herein by reference, comprises a visual environment simulator in which three separately positioned ultrasonic transmitters send signals to each of three ultrasonic receivers in order to monitor the change in the spatial coordinates and the orientation angles of the viewer and/or mobile unit carrying the viewer. 
   SUMMARY OF THE INVENTION 
   It is an object of the present invention to provide an improved ultrasonic object tracking system. 
   It is a further object of some aspects of the present invention to provide a catheter location system which is based on ultrasound emission from the catheter&#39;s distal end and which does not require a wired connection to the distal end. 
   Preferred embodiments of the present invention are based on the interaction of electromagnetic (RF) and ultrasonic energy fields. An RF-responsive transducer, having a resonant vibrational frequency in the ultrasonic range, is fixed to an object and is irradiated with an RF energy field. The transducer is induced to vibrate and emits energy, either RF or ultrasonic energy, or both, responsive to an interaction of the RF field with the vibration. The emitted energy is detected and is used to determine position and/or orientation coordinates of the object. 
   In some preferred embodiments of the present invention, the transducer emits ultrasonic waves responsive to the RF field impinging thereon. The emitted ultrasound waves are detected by a plurality of ultrasound detectors, preferably three or more. A processor receives signals from the ultrasound detectors and processes them to determine the position and/or orientation of the object, using triangulation, time-of-flight measurement, or other suitable methods of position determination, as are known in the art. There is preferably no wired connection between the transducer and the detectors, the processor or any other elements of the apparatus. 
   In some of these preferred embodiments, the transducer comprises one or more piezoelectric crystals, each having a respective resonant frequency, and one or more foil members coupled to each crystal. Although in the preferred embodiments described herein, the transducer comprises foil members, it is understood that other conductive materials could also be used. One or more RF radiators generate RF signals at or near each of the resonant frequencies in a vicinity of the crystals, causing the foil members to vibrate and emit ultrasound waves at a characteristic frequency for each crystal/foil unit. 
   In a preferred embodiment of the present invention, the transducer comprises three crystal/foil units, having respective, mutually substantially orthogonal axes. Each unit is constructed and mounted such that its resonant frequency is different from that of the other two units. In this embodiment, the RF generators generate fields at each of the three resonant frequencies, either simultaneously or in a continuous cycle through the three frequencies. Using methods known in the art, some of which are described, for example, in PCT patent publication WO 96/05768, the three components of the angular orientation vector of the object, as well as the three position vector components, are then calculated based on the signals from the ultrasound detectors. 
   Although the anti-theft system described in the above referenced U.S. Pat. No. 3,713,133 uses radio frequency (RF) irradiation to produce ultrasonic emission in a manner similar to the present invention, the anti-theft system is capable only of reporting the presence or absence of a target, and cannot be used to locate and track an object. 
   In some preferred embodiments of the invention, the transducer is incorporated into an invasive medical instrument such as a catheter, endoscope, trocar, or laparoscope. In one of these preferred embodiments, the transducer is fixed to the distal end of a trocar through which a laparoscope is passed in abdominal surgery. The position of the distal end is determined so as to prevent injury to underlying bowel and blood vessels, in particular the common iliac vein. In another preferred embodiment, the location of the distal end of a Swan-Ganz catheter being inserted into the internal jugular vein is continuously monitored in order to decrease the likelihood of puncture injury of the carotid artery or the pleural cavity. 
   In still another preferred embodiment, the precise placement of a stent into the descending aortic artery in treatment of an aortic aneurysm is made possible by incorporating one or more transducers units into the distal end of the catheter placing the stent. In this embodiment, knowing the angular orientation of the catheter is important in addition to knowing its spatial location because of the need to avoid placing the stent in a manner which blocks the lumbar arteries supplying the spinal cord. Furthermore, since there is no wired connection needed between the transducers and other elements of the position sensing system, one or more of the transducers could be fixed to the stent and used to determine its position and orientation before, during and after placement by the catheter. The use of stents incorporating wireless transducers is described further in PCT patent application PCT/IL97/00447, which is assigned to the assignee of the present patent application and is incorporated herein by reference. 
   In a further preferred embodiment of the present invention, one or more of the transducers are incorporated in a probe designed to destroy a tumor, thereby allowing the physician to know the precise location and orientation of the probe with respect to known coordinates of the tumor. A particular application of this preferred embodiment is the removal of a pituitary tumor by heat, cold, or other means. Surgical probes using position sensors are described, for example, in the following PCT patent applications: PCT/US97/022443, PCT/IL97/00058 and PCT/IL97/00059, which are incorporated herein by reference. 
   In distinction to active ultrasound-based position-sensing systems known in the art, in the present invention ultrasound waves are generated passively at the probe. This method of ultrasound generation is advantageous because there is no need for wires leading from the probe to either an outside power source (as in U.S. Pat. No. 5,412,619) or to signal amplifiers and a signal processor (as in patent publication WO 96/05768 and U.S. Pat. No. 4,807,202). An additional advantage of the passive generation of ultrasound in this invention compared to some other currently used methods is that there is no potentially disruptive background ultrasound radiation created by irradiation from outside the body. Ultrasound radiation at the resonant frequency comes only from the transducer, typically from the crystal/foil unit described above. An advantage deriving from the unit&#39;s very small size, as well as from the lack of additional hardware required within the probe, is that the invasive medical instrument can be made small and flexible compared to other types of emitters and detectors used in position sensing systems known in the art. Additionally, the use of such a probe in an invasive medical instrument obviates exposure of the patient to potentially harmful ionizing radiation which is often used to determine the location of an instrument within the patient&#39;s body. 
   In other preferred embodiments of the present invention, the transducer comprises a diaphragm which vibrates at the resonant frequency. Using methods similar to those described in U.S. Pat. No. 3,713,133, such as the embodiment shown in  FIG. 4  thereof, ultrasound with a frequency substantially similar to the resonant frequency of the diaphragm is generated by an ultrasound generator at a known location and is directed towards a vicinity of the transducer. The diaphragm mechanically vibrates at its resonant frequency in response to the externally applied ultrasound radiation. A radio frequency (RF) field of substantially higher frequency is initially generated in a vicinity of the sensor either before or at substantially the same time as the time when the ultrasound field is initiated. A portion of the RF radiation is modulated responsive to the mechanical vibration of the diaphragm. The modulated RF signal is detected by an RF detector and is used to determine the position of the object. 
   In U.S. Pat. No. 3,713,133, detection of the modulated RF signal is used to trigger an alarm indicating that the presence of a diaphragm has been detected. No additional information is derived from the modulated RF signal. In accordance with a preferred embodiment of the present invention, the radiated and detected RF and ultrasound signals are used to calculate the location of the diaphragm, as described hereinbelow. A time period starting from the initiation of ultrasound field generation and ending when a modulated RF signal is first detected at the RF detector is substantially the same as the “time of flight” which ultrasound takes to traverse the distance from the ultrasound generator to the diaphragm. A signal processor calculates the distance from the ultrasound generator to the diaphragm based on the measured “time of flight” and the speed of sound in tissue. Repeating this process using, in sequence, two or more additional ultrasound generators at known points in space yields the distance from the diaphragm to three known points, and allows the signal processor to calculate the location of the object with respect to an external reference frame. 
   In some additional preferred embodiments of the present invention, three non-collinear diaphragms are fixed at known positions to the object, each diaphragm having a substantially different resonant frequency from that of the other diaphragms. The location of each diaphragm is found using the procedure described above, this calculation thereby yielding the angular orientation of the sensor. 
   The present invention will be more fully understood from the following detailed description of the preferred embodiments thereof, taken together with the drawings, in which: 

   
     BRIEF DESCRIPTION OF THE DRAWINGS 
       FIG. 1  is a schematic illustration of a catheter tracking system, in accordance with a preferred embodiment of the present invention; 
       FIG. 2A  is a schematic illustration of the distal end of a catheter, for use in the system of  FIG. 1 , in accordance with a preferred embodiment of the present invention; 
       FIG. 2B  is a schematic illustration of a transducer, for use in the system of  FIG. 1 , in accordance with a preferred embodiment of the present invention; 
       FIG. 2C  is a schematic illustration of the distal end of a catheter, for use in the system of  FIG. 1 , in accordance with another preferred embodiment of the present invention; 
       FIG. 3A  is a schematic illustration of the distal end of a catheter, for use in the system of  FIG. 1 , in accordance with another preferred embodiment of the present invention; 
       FIG. 3B  is a graphical illustration of parameters used in calculating angular coordinates of the catheter shown in  FIG. 3A ; 
       FIG. 4  is a cross-sectional view of the catheter of  FIG. 3A ; 
       FIG. 5  is a cut-away, simplified pictorial view of the catheter of  FIG. 3A ; 
       FIG. 6  is a block diagram of circuitry used to determine six-dimensional coordinates of the catheter shown in  FIG. 3A , in accordance with a preferred embodiment of the invention; 
       FIG. 7  is a schematic illustration of the distal end of a catheter, for use in the system of  FIG. 1 , in accordance with another preferred embodiment of the present invention; 
       FIG. 8  is a cross-sectional view of a transducer, as used in the distal end of the catheter shown in  FIG. 7 ; 
       FIG. 9A  is a schematic illustration of the distal end of a catheter, for use in the system of  FIG. 1 , in accordance with another preferred embodiment of the present invention; and 
       FIG. 9B  is a schematic illustration of the distal end of a catheter, for use in the system of  FIG. 1 , in accordance with yet another preferred embodiment of the present invention. 
   

   DETAILED DESCRIPTION OF PREFERRED EMBODIMENTS 
     FIG. 1  is a schematic representation of a system  20  for tracking the position of a catheter  22  in the body of a human or non-human subject, in accordance with a preferred embodiment of the present invention. In this application, catheter  22  is inserted through a blood vessel  18  of a patient using standard techniques. Catheter  22  comprises a body  14 , a locating transducer  12 , and an active portion  10  at the distal end of the catheter. The active portion, in accordance with various preferred embodiments of the invention, may include an electrical sensor, an ultrasound head, a fiber optic viewing head, an electrical stimulator, an electrical or laser ablator, an ionic sensor, an oxygen or carbon dioxide sensor, an accelerometer, a blood pressure or temperature sensor, or a cryogenic probe, as are known in the art. In general, the catheter will include leads, light guides, wave guides, etc., for energizing the active portion in response to commands of an operator, and may also include a tip deflection mechanism, for steering the catheter inside the body. 
   The position and/or orientation of the distal end of the catheter is obtained by determining the position and/or orientation of transducer  12 , which preferably comprises from one to three crystal/foil units, such as those shown below in  FIGS. 2A ,  2 C, and  3 A. Such units resonate and emit ultrasonic radiation when subjected to RF irradiation of an appropriate frequency, as described in U.S. Pat. No. 3,713,133, particularly with reference to FIG. 4B thereof. 
   The RF radiation is initiated by control signals from a control unit  32  which cause an RF radiator driver  26  to generate driving signals. The driving signals in turn cause one or more RF radiators  40 ,  42  and  44  located outside a body surface  24  of the patient to emit RF radiation. A representation of the driving signals is also sent to a signal processor  30 . The ultrasonic radiation from locating transducer  12 , generated by one or more resonating crystal/foil units, is detected by a plurality of ultrasound detectors  34 ,  36 , and  38 . Other elements shown in  FIG. 1 , such as ultrasound generators  11 ,  13  and  15 , are described below with reference to other embodiments of the present invention. 
   The detectors are arranged such that signal processor  30  can utilize inputs comprising the representation of the driving signals and measurements from detectors  34 ,  36 , and  38  in performing a triangulation algorithm, as is known in the art, in order to calculate the position of locating transducer  12 . Detectors  34 ,  36 , and  38  may be arranged in any convenient position and orientation, but it is preferable that (a) they are fixed in respect to some reference frame; (b) they are non-overlapping, that is, there are no two detectors with the exact, identical location and orientation; (c) the detectors are not placed collinearly; and (d) two detectors and the locating transducer are at no time all collinear. 
   It should be understood that placement of detectors  34 ,  36 , and  38  and the number of resonating units to be incorporated in the locating transducer  12  will vary according to each application of the invention. In particular, some preferred applications of the present invention require precise knowledge of the orientation of the catheter (e.g. laser ablation), while others only require knowledge of the position of the catheter (e.g. gastrointestinal tract tube placement). 
   The ultrasonic signals generated by transducer  12  are transduced by detectors  34 ,  36 , and  38 , into electrical signals which are passed to signal processor  30 , in either analog or digital form. Signal processor  30  processes the outputs of the detectors to calculate the position and/or orientation of the locating transducer  12 , and transmits this information to a display monitor  28  and/or control unit  32 . 
   In practice, the active end of the catheter may be used to gather information, such as ultrasound echo information, electrical activity information, etc., and optionally to perform certain procedures on the arteries (or veins) or other tissue within an organ chamber  16  to which the artery (or vein) leads. Particular examples of organ chambers are the chambers of the heart, brain, or gastrointestinal tract. 
   Reference is now made to  FIGS. 2A , and  2 B.  FIG. 2A  is a schematic illustration of the distal end of catheter  22 , in accordance with a preferred embodiment of the present invention. In this preferred embodiment, transducer  12  comprises a crystal/foil unit  112 , shown in detail in  FIG. 2B , which comprises a piezoelectric crystal  52  and foil members  92  and  93  coupled to crystal  52 . Crystal/foil unit  112  is mounted in catheter body  14  such that an axis  53  of unit  112  is parallel to a longitudinal axis of the catheter. As described in the above-mentioned U.S. Pat. No. 3,713,133, the RF field produced by RF radiator  40  causes ultrasonic resonance in crystal/foil unit  112 . Radiators  42  and  44  generally need not be utilized in this preferred embodiment. In response to the RF field, unit  112  emits acoustic radiation, which is detected by detectors  34 ,  36 , and  38 , each of which sends signals corresponding thereto to signal processor  30 . 
   The signal processor preferably uses the initiation time of the driving signal to RF radiator  40 , the time of arrival at each detector of the acoustic radiation from unit  112 , and the speed of sound in tissue, in order to determine the distances from the unit  112  to each of the detectors. The initiation time of a driving signal is substantially the same time as that when acoustic radiation leaves a crystal/foil unit, so the signal processor calculates the “time of flight” of acoustic radiation from unit  112  to each of the detectors, and multiplies each of these times by the speed of sound in tissue to yield the distances from unit  112  to each detector. With these distances, signal processor  30  calculates three-dimensional position coordinates of transducer  12  with respect to a reference frame, using methods known in the art. 
     FIG. 2C  is a schematic illustration of the distal end of catheter  22 , in accordance with another preferred embodiment of the present invention. In this preferred embodiment, major axes  63  and  65  of two crystal/foil units  114  and  116  are continuous with the longitudinal axis of the catheter. Unit  114  comprises a piezoelectric crystal  62  which has a resonant frequency, a first foil member  94  coupled to a first side of crystal  62 , and a second foil member (not shown) coupled to a second side of crystal  62 . Unit  116  comprises a piezoelectric crystal  64  which has a resonant frequency substantially different from that of crystal  62 , a first foil member  96  coupled to a first side of crystal  64 , and a second foil member (not shown) coupled to a second side of piezoelectric crystal  64 . Preferably, the physical dimensions and/or rigidity of the foil members coupled to crystal  62  are accordingly substantially different from those of crystal  64 . Using methods described hereinbelow, the ultrasound emissions from crystal/foil units  114  and  116  are distinguished by signal processor  30 , and the spatial location of each unit is determined with respect to a reference frame. Calculation of the three-dimensional position coordinates of each of units  114  and  116  determines both the location of the catheter and the orientation of its longitudinal axis. 
     FIGS. 3A ,  4 , and  5  are schematic illustrations of the distal end of catheter  22 , in side, sectional and isometric views, respectively, in accordance with another preferred embodiment of the present invention. In this preferred embodiment, transducer  12  comprises three crystal/foil units  118 ,  120 , and  122 , wherein each unit comprises a piezoelectric crystal and two foil members as described hereinabove. The respective resonant frequencies of units  118 ,  120 , and  122  are substantially different from one another, the different resonant frequencies being attained using methods similar to those used for the embodiment shown in  FIG. 2C . Preferably, crystal/foil units  118 ,  120 , and  122  have substantially mutually orthogonal axes  55 ,  57 , and  59 , respectively, with axis  55  parallel to but not necessarily collinear with the longitudinal axis of catheter  22 . In this embodiment, the differences in one or more aspects of the signals received from any particular crystal/foil unit (e.g. signal strength or signal timing) as detected by detectors  34 ,  36 , and  38 , are used to calculate one component of the angular orientation vector of the catheter, as described below. 
     FIG. 3B  shows parameters according to which the angular orientation of crystal/foil unit  118  in  FIG. 3A  is calculated from the detected ultrasound waves. In this example, transducer  12  is assumed to be located in tissue whose acoustic properties are substantially homogeneous and isotropic, and wherein emission properties of the crystal/foil unit are such that measurement of the magnitude of acoustic radiation emitted from the unit varies as a function f(i), where i is the angle formed between vectors n and d i , n being orthogonal axis  55  of the unit, and d i  (i=1, 2, or 3) being a vector extending from the center of the unit to one of detectors  34 ,  36 , or  38 , respectively. Preferably, the Newton-Raphson method or another multiple iteration algorithm uses the known location of the unit (determined, for example, as described above) and measurements m 1 , m 2 , and m 3  of the magnitude of the radiation from the unit made by each of the three detectors to find n, the axis of the unit. 
   The iterative process for finding n preferably comprises guessing an initial vector v, determining the angles  1 ,  2 , and  3  between v and each of the three vectors d 1 , d 2 , and d 3 , and calculating an error function E(v) based on how closely measurements m 1 , m 2 , and m 3  made at angles  1 ,  2 , and  3  fit f(i). Using methods well known in the art, successive refinements of v yield an estimate substantially equivalent to n, the orthogonal axis of the unit. Execution of this calculation for crystal/foil units  118 ,  120 , and  122  is sufficient to entirely determine the angular orientation of the catheter. 
   In some preferred embodiments of the present invention, one surface of each crystal/foil unit is coupled to an ultrasound absorber (not shown), which is substantially ultrasound-opaque, in order to substantially attenuate ultrasound radiation emitted in the direction of the absorber. Signal processor  30  integrates the presence of the absorber into calculations determining the angular orientation of the catheter which use the method presented above, in order to distinguish among possible reflected orientations of the catheter that could produce the same detector measurements. 
   Preferably, as shown in  FIG. 4 , crystal/foil units  118 ,  120 , and  122  are non-collinear. In this case, by determining the absolute location of three known points on or within a solid object, the angular orientation of the object can also be calculated in place of or in addition to the aforementioned orientation calculation based on the magnitude of the signal emitted from each crystal/foil unit. These two methods can be used together to increase the accuracy and reliability of the calculation of the angular orientation of the catheter. 
   For most aspects of the present invention, quantitative measurement of the position and/or orientation of the distal end of the catheter  22  relative to a reference frame is necessary. This requires: 
   at least two non-overlapping crystal/foil units, which generate at least two distinguishable ultrasonic signals, the positions and orientations of the units being known with respect to each other and with respect to the catheter; 
   at least one RF radiator  40  which generates the field which causes the units to resonate; and 
   at least three non-overlapping, noncollinear detectors  34 ,  36 , and  38 , capable of detecting and transducing the time, magnitude, frequency and/or phase information of the ultrasound waves at the fixed points where each of the detectors is located. 
   In a preferred embodiment of the invention, crystal/foil units  118 ,  120 , and  122  each have a longest dimension of 0.3 mm to 3.0 mm. It will be understood that these dimensions may vary over a considerable range and are only representative of a preferred range of dimensions. 
     FIG. 6  is a block diagram showing circuitry  84  used in computing the position of locating transducer  12 , in accordance with the preferred embodiment of the present invention shown in  FIG. 3A . In this embodiment, RF radiators  40 ,  42 , and  44 ; crystal/foil units  118 ,  120 , and  122  (shown in  FIG. 3A ); and detectors  34 ,  36 , and  38  are used to determine the six-dimensional coordinates of locating transducer  12 . Control unit  32  utilizes D/A converters  60 ,  62 , and  64  to generate three sine waves of three different frequencies which are input separately to signal amplifiers  66 ,  68 , and  70 . RF radiator driver  26 , whose output comprises the outputs of amplifiers  66 ,  68 , and  70 , generates signals which cause RF radiators  40 ,  42 , and  44  to radiate at frequencies which cause crystal/foil units  118 ,  120 , and  122  respectively to resonate and emit acoustic radiation. Alternatively, one or more of the RF radiators transmit a signal including all of the appropriate frequency components. 
   The acoustic radiation emitted by each of units  118 ,  120  and  122  in transducer  12  is detected by each of the detectors, which output signals responsive thereto to amplifiers  78 ,  80 , and  82 . The amplifiers then convey amplified signals representing the detected acoustic radiation to signal processor  30 . Using methods known in the art, for example a Fast Fourier Transform of the detector signals, signal processor  30  calculates for each detector the components of the signal which are due to each of units  118 ,  120  and  122 . Alternatively, irradiation at the appropriate frequencies occurs in a repeated cycle through each frequency, such that signal processor  30  performs position and orientation calculations for each unit in sequence. 
   Control unit  32  comprises an assemblage of components to perform intended functions. For example, such components may receive information or signals, process information, function as a controller, display information on a monitor  28 , and/or generate information or signals. Typically, control unit  32  comprises one or more microprocessors. 
     FIG. 7  is a schematic illustration of locating transducer  12  which comprises a tag  140 , in accordance with another preferred embodiment of the present invention. Tag  140  comprises a diaphragm  144  which has a resonant frequency and a frame  142  which is coupled to a rim of diaphragm  144 , so that the diaphragm is firmly mounted and able to vibrate. Preferably, diaphragm  144  comprises a metal film. 
     FIG. 8  shows a cross-sectional view of tag  140 . Although  FIGS. 7 and 8  show one preferred way in which diaphragm  144  may be mounted in frame  142 , it will be understood that other arrangements are also possible. For example, in other preferred embodiments (not shown in the figures), one edge of the diaphragm is coupled to the frame, and an opposite edge of the diaphragm is free to vibrate. 
   Referring again to  FIGS. 1 and 7 , ultrasound with a frequency substantially similar to the resonant frequency of diaphragm  144  is generated outside of body surface  24  of the patient by ultrasound generator  11  situated at a known location and is directed towards a vicinity of locating transducer  12 . The diaphragm mechanically vibrates at its resonant frequency in response to the externally applied ultrasound radiation. RF radiator  40  begins to generate an RF field at a frequency substantially higher than the resonant frequency before or at substantially the same time as the time at which generation of the ultrasound field is initiated. A portion of the RF radiation incident on tag  140  is modulated responsive to the mechanical vibration of the diaphragm. An RF detector  17  located outside of the body surface of the patient detects the RF radiation, and processor  30  separates and detects a modulated RF signal from the unmodulated RF background. 
   It will be appreciated that although ultrasound generator  11  is shown, for clarity as being a separate unit from detectors  34 ,  36  and  38 , the same type of element may be used for both functions. Similarly, RF detectors  40 ,  42  and/or  44  may also perform the function of RF detector  17 . 
   The time period starting from the initiation of ultrasound field generation and ending when the modulated RF signal is first detected at the RF detector is substantially the same as the length of time which ultrasound takes to traverse the distance from the ultrasound generator to the diaphragm. Signal processor  30 , having inputs corresponding to the externally applied ultrasound and RF fields and the detected RF signal, calculates the distance from the ultrasound generator to the diaphragm based on the measured “time of flight” and the speed of sound in the tissue. Repeating this process using, in sequence, two additional ultrasound generators  13  and  15 , located at known points in space, yields the distance from the diaphragm to three known points, and allows the signal processor to calculate the location of the transducer with respect to a reference frame. 
     FIG. 9A  shows a preferred embodiment of the present invention in which locating transducer  12  comprises two tags  160  and  170 , axes  166  and  176  of which are generally aligned with the longitudinal axis of the catheter. Tags  160  and  170  comprise diaphragms  164  and  174 , respectively, which have different resonant frequencies. Using methods similar to those described above, the location of each diaphragm is calculated, and the angular orientation of the longitudinal axis of the catheter is thereby determined. 
     FIG. 9B  shows a schematic illustration of another preferred embodiment of the present invention, in which locating transducer  12  comprises three non-collinear tags  190 ,  200 , and  210  fixed at known positions to the transducer. Tags  190 ,  200 , and  210  comprise diaphragms  194 ,  204 , and  214 , respectively, each diaphragm having a substantially different resonant frequency from that of the other diaphragms. In this embodiment, the location of each diaphragm is found using the procedure described above, this calculation thereby yielding the angular orientation of the transducer. 
   Although preferred embodiments are described hereinabove with reference to a catheter, it will be understood that the principles of the present invention may be used in position and/or orientation detection of other types of objects, as well. The preferred embodiments are cited by way of example, and the full scope of the invention is limited only by the claims.