Abstract:
The present invention is directed to a device and method for opening obstructed body internal passages and for sensing and characterizing tissues and substances in contact with the device. In general, the device comprises a catheter tube capable of inducing vibrations in a guidewire contained therein, wherein said vibrations of the guidewire are utilized for opening a passage through an occlusion. The in-vivo vibrations may be induced by means of a magnetic field actuating means and a guidewire comprising magnetic coupling means, or by means of transducers, which may be also used for the sensing. The invention also relates to the field of minimal invasive catheterization, particularly an apparatus for opening and/or removing obstructions occluding body internal passages by means of an active guidewire comprising a coil to which an alternating voltage can be applied. In that way the guidewire can vibrate if an external magnetic field is applied.

Description:
RELATED APPLICATIONS 
     This Application is a CIP of U.S. patent application Ser. No. 11/914,095, filed Jul. 8, 2008 now U.S. Pat. No. 8,295,908, which claims the benefit of PCT/IL2006/000541, filed May 9, 2006, which claims the benefit of IL 168568, filed May 11, 2005, IL 168569, filed May 11, 2005, and IL 170412, filed Aug. 22, 2005. This application is also a CLP of U.S. patent application Ser. No. 12/516,431, filed Mar. 10, 2010 now abandoned, which claims the benefit of PCT/IL2007/001435, filed Nov. 21, 2007, which claims the benefit of IL 179618, filed Nov. 27, 2006. 
    
    
     FIELD OF THE INVENTION 
     The present invention relates to the field of minimal invasive catheterization. More particularly, the invention relates to a method and apparatus for opening and/or removing obstructions occluding body internal passages and for in vivo sensing of substance/tissue in body internal passages and body organs. 
     In particular, the invention relates to an apparatus for opening and/or removing obstructions occluding body internal passages by means of an active guidewire. More particularly, the invention relates to an active oscillating guidewire, capable of passing through an occluded vessel. 
     BACKGROUND OF THE INVENTION 
     Many vasocclusive events, such as heart attacks and strokes, are caused by plaque build-ups in arteries. As one specific example, atherosclerotic plaque is known to build-up in the walls of arteries in the human body. Such plaque build-up restricts circulation and often causes cardiovascular problems, especially when the build-up occurs in coronary arteries. 
     One common method for opening partially occluded body internal passages is to guide a medical device to the diseased site, where it is used to carry out the needed treatment. A guidewire is usually used for advancing a catheter device thereover via body internal passages towards the treatment site. Typically, the distal tip of the guidewire is introduced into the body of the treated subject via an incision and advanced therethrough towards the treatment site, thereby forming a path leading to the occluded site through said body internal passages. The catheter, or any other suitable treatment devices (e.g., balloon catheter, stent or rotational atherectomy device), may be then threaded over the guidewire and advanced through said internal passages using the guidewire as a rail. 
     Total or near-total occlusions in body internal passages can, partially or entirely, block the passage therethrough. For example, in patients who suffer from coronary CTO (chronic total occlusion), the successful performance of a Percutaneous Transluminal Coronary Angioplasty (PTCA) is a technical challenge. The factor that is most determinative of whether the practitioner can successfully perform PTCA on patients suffering from coronary CTO is his ability (or inability) to advance a suitable guidewire from a position proximal of the lesion to a position distal of the lesion while remaining inside the true vessel lumen (without performing perforation or dissection of the artery wall). 
     In some instances, such as where the occlusive matter is soft or where the body internal passage is partially occluded, the guidewire can easily be pushed through the occlusive matter itself, thereby allowing the guidewire to remain within the body internal passage. However, in other cases, such as when the body internal passage is totally occluded by hard plaque (e.g., calcified atherosclerotic plaque), the guidewire cannot cross the occlusion and may deviate to the side and penetrate through layers of the passage walls (e.g., the intima—inner layer of a vessel wall), thereby creating a neo-lumen therethrough (e.g., through the sub-intimal space—within the wall of the artery between the intima and media, or adventitia, i.e. a dissection), or even completely exit said internal passage, i.e. a perforation. 
     Several techniques are known for passing through an occluded internal passage, such as laser catheters (U.S. Pat. No. 6,673,064), ultra sonic catheters (U.S. Pat. No. 6,702,748), and tissue displacement or hinged expansion devices (U.S. Pat. No. 6,800,085). In all of those techniques the occlusion is opened by means of a catheter device equipped with operative means for occlusions opening. However, the prior art devices suffer from lack of flexibility and maneuverability due to the bulky structure of their catheter devices. Consequently, the treatment procedures which utilize these prior art devices are substantially different from conventional catheterization procedure workflow as commonly practiced in regular cases (non CTO cases). 
     The aforementioned prior art solutions also suffer from lack of ability to indicate to the practitioner in real time, i.e. while carrying out the procedure, whether he is navigating the treatment devices through the occlusion (true lumen) or if he is actually perforating or dissecting the body internal passage, e.g. the artery. 
     Other known procedures, such as described in U.S. Pat. No. 6,852,109, propose a method for forming a passage through the CTO by a guidewire having active Radio Frequency (RF) ablation tip, with Optical Coherence Reflectometry (OCR) capability for sensing the position of the tip. However this known type of guidewire is a special guidewire comprising a mechanism for transferring RF energy and a following catheter with fiber optics for the OCR capability. These restraints are relatively rigid and therefore diminish the flexibility of the device, which is an important feature for carrying out in vivo navigation. Thus, also this prior art device suffers from lack of flexibility, and the need to deviate from the conventional practice workflow of the practitioner. 
     Another solution used for determining whether an organic tissue is healthy or not is using IVUS (intravascular ultrasound), for example as described in U.S. Pat. Nos. 6,685,644 and 6,685,643, however lack of data due to poor transmission in this known method and calcified build-ups that cause “acoustic shadowing” yield poor results in determining tissue type and true lumen detection. 
     In still another solution used such as described in U.S. Pat. No. 5,908,395, a hand held vibrator is attached to the proximal side of a guide wire, or a catheter through which the guidewire is threaded. 
     The guidewire then conveys the proximal vibrations to its distal end, subject to the specific passage of the guidewire through the arteries. If indeed these vibrations reach the distal end of the guidewire they may be efficient in penetrating and recanalization of CTOs (chronical total occlusions). However, there is a problem in that the vibrations may be absorbed before reaching the distal end. In addition, using an external hand held vibrator interferes with the standard operation of the guidewire, and limits the operator from conveniently controlling the guidewire by manually holding its proximal end, again causing the need to deviate from the conventional practice workflow of the practitioner. 
     There thus exists a need for devices and techniques for treating occluded body internal passages, for characterizing the tissue/substance the treatment device is in contact with and determining its location within and about the body internal passage, and for safely opening occlusions therein without damaging the occluded internal passage. 
     It is therefore an object of the present invention to provide a method and device for opening occluded body internal passages and/or body organs. 
     It is another object of the present invention to provide a method and device for safely navigating treatment means, such as a catheter device, to a treatment site through body internal passages. 
     It is a further object of the present invention to provide a method and device for in vivo characterizing the tissue and/or substance being in contact with a treatment device. 
     It is yet another object of the present invention to provide a catheter device capable of inducing vibrations in a guidewire contained therein. 
     In still another solution used as described in copending application PCT/IL2006/000541, a device comprises a magnetic guidewire housed in a coiled catheter. The guidewire is vibrated by feeding electrical current via the coils of the catheter, thus providing magnetic excitation of the guidewire tip. However, because of the magnetic guidewire structure and dimensions this solution may not be optimized to match the physician procedure. The magnets beads added to the guidewire may increase the diameter thereof, and may thusprevent the use of some devices that are threaded onto regular guidewires. 
     More particularly, these over-the-wire devices sometimes have a lumen that is only marginally larger in diameter than the diameter of the guidewire. By adding magnets to the guidewire, these over-the-wire devices may not suited to be threaded onto the magnetic guidewire, as the diameter of the magnets may be bigger than the inner diameter of the lumen of the catheter. 
     In still another solution used such as described in WO 00100252, a catheter or guidewire that is made from ferromagnetic means and is positioned such that a predetermined portion of the device lies adjacent to the target site. A magnetic field source that changes over time in magnitude and/or direction, of sufficient strength is disposed outside the patient&#39;s body in sufficient proximity to the intrabody device to induce motion in the device through the oscillating magnetic field that it emits. However this method significantly deviates from the physician regular workflow and requires the change of the catheterization lab in order to facilitate the magnet field exterior device, furthermore, it is almost impossible to guarantee that the magnetic member that lies within the body cavity will be exactly adjusted to the magnetic source. 
     In still another solution such as described in WO 94/12234, a flexible elongate device having a distal extremity with a vibratory impact tip embedded with a coil spring piston like mechanism for catheters and guide wires. However, because of the fact the guidewire or catheter are embedded with a spring coil vibrational mechanism, the mechanical properties of the guidewire and the catheter significantly change and the ability to pass over the wire devices is reduced, thus deviating from the standard workflow of the procedure. 
     Several uses of magnetic coupling of guidewires are known, such as in U.S. Pat. No. 5,813,996, however this known coupling is static and is used as a guide wire extension system including a guide wire and an extension wire and means for magnetically coupling the guide wire to the extension wire, and not as a means for magnetic vibration for gateway passage opening. 
     There thus exists a need for devices and techniques for treating occluded body internal passages, for characterizing the tissue/substance the treatment device is in contact with, for determining its location within and about the body internal passage, and for safely opening occlusions therein without damaging the occluded internal passage, while keeping the same work flow (clinical procedure), and enabling the physician to use exactly the same over-the-wire devices. 
     Further more, guidewires are a great technical and clinical challenge. The structure of the guidewire, and generally speaking composition of materials and dimensions of the different segments of the guidewire set the guidewire&#39;s characteristics. More specifically, most guidewires are constructed such that their distal portions (typically the distal 100-300 mm of the guidewire) are made of a specially shaped and tapered core, wrapped with a special spring-like coil. This coil, together with the inner shaped core of the guidewire influences dramatically the behavior and characteristics of the guidewire. 
     Therefore, it is desirable to be able to make use of the existing structure of conventional guidewires, and thus maintaining the critical mechanical characteristics of the guidewire, while adding the capability to generate an alternating magnetic field. 
     This alternating magnetic field can then serve to generate alternating magnetic forces that oscillate the tip of the guidewire providing it with active drilling capabilities to open occlusions. 
     It is an object of the present invention to provide a method and device for opening occluded body internal passages and or body organs, by providing additional means and implementing the coils already embedded into a guidewire in such a way so as to enable electrical generation of alternating magnetic fields. 
     Other objects and advantages of the invention will become apparent as the description proceeds. 
     SUMMARY OF THE INVENTION 
     The present invention is directed to a device and method for opening obstructed body internal passages and for sensing and characterizing tissues and substances being in contact with the device of the invention. In general, the device of the present invention comprises a catheter tube capable of inducing vibrations in a guidewire contained therein, wherein said vibrations of the guidewire are utilized for opening a passage through an occlusion. 
     More particularly, the present invention relates to a device and method for in vivo drilling in living tissue and/or finding the weak path in said living tissue, in body internal passages and body organs, which may be utilized for opening a passage suitable for passing a treatment device (e.g., a stent, balloon) through an occluded body internal passage (e.g., blood vessel), such as in cases of total occlusion (Chronic Total Occlusion—CTO). The in vivo drilling is performed by means of a unique drilling guidewire, which aside from drilling through the occlusion can enable the operator to sense the tissue/substance being in contact with the drilling part of said drilling guidewire. The sensing of the tissue/substance contacting the drilling guidewire may be advantageously used to provide an indication as to whether the drilling guidewire properly operates in the occluded internal passage or whether it deviates therefrom and injures the passage wall. The path drilled and/or opened and/or re-canalized through the occluding matter enables the passage of a conventional guidewire through the occluded passage and thereby allows carrying out the conventional treatments applicable in such cases, such as, for example, by means of balloon catheters and stents. 
     The drilling according to this invention is carried out by means of rapid vibrations e.g., at a frequency of about several dozens of Hz, preferably in the region of 1-200 Hz, low amplitude vibrations e.g., with an amplitude of about a fraction of a mm, preferably in the region of 0.1 to 1 mm, that are directed in vivo to the occluding matter. The in vivo drilling device of the invention is designed to transfer the drilling energy with high efficiency into hard/calcified tissue, while keeping the efficiency low, when drilling into relatively soft elastic tissues. The drilling vibrations are preferably limited to low amplitudes, resulting in a drilling scheme that transfers energy very efficiently into hard/calcified occlusions. At the same time, such drilling cannot transfer energy efficiently into soft elastic tissues, such as the artery wall, thus lowering the risk of perforation or dissection thereof. 
     The in vivo drilling device of the present invention is preferably implemented by a guidewire comprising magnetic coupling means adapted for inducing axial vibrations therein by means of an alternating magnetic field. The magnetic coupling means may be implemented by a number of miniature magnetic elements (e.g., having a ring shape) radially attached to a section of a conventional guidewire or embedded within some segments of the guidewire itself. By applying rapid alternating/changing magnetic fields around the guidewire section that comprises said miniature magnets rapidly vibrate that guidewire section. 
     The alternating/changing magnetic field may be induced by alternating the frequency and magnitude (amplitude and direction) of the magnetic field. The magnetic field may be applied in vivo by a catheter device comprising a magnetic field actuating means mounted in section thereof corresponding to the location of the magnetic coupling means on the drilling guidewire. For example, the alternating magnetic field may be applied by a coil wound on (or in) a section of a catheter device (or embedded therein) containing the drilling guidewire. An alternating magnetic field may be electrically applied by connecting the coil to an alternating electrical current source, which in effect vibrates the guidewire. 
     Additionally or alternatively, the alternating magnetic field is applied by vibratable fixed magnets mounted in a section of a catheter device comprising the drilling guidewire, and in a location corresponding to the location of the coupling magnets on the drilling guidewire or embedded in it. In particular, these vibratable fixed magnets can be attached to the catheter and have the shape of hollow cylinders, through which the guidewire passes. The vibration of the vibratable fixed magnets attached to the catheter may be achieved by means of electrically vibratable means, such as piezoelectric elements, which are attached to the magnets, wherein said electrically vibratable means can be powered by an external electrical power source. The power source may be of many forms, but preferably has a sinusoidal shaped output with alternating amplitude and frequency, thus providing vibrations of different characteristics. 
     The frequency of the vibrations may be changed in close loop in order to manually or automatically reach the resonance frequency or anti-resonance of the whole apparatus, thus gaining continuous leveling of the drilling energy. 
     The catheter device may include several separated electro-magnet coils. Each of those coils may be independently powered by an electrical current. Thus, by applying exciting current to each coil successively, (e.g., in a “wave” manner)—it is possible to achieve a relatively constant power over long range along the catheter/guidewire (e.g., as in linear stepping motor). 
     The electrical power (current and voltage vs. frequency) fed into the vibrating elements, can be analyzed to measure the overall apparatus magnetic impedance, and thereby provide an indication about the type of tissue/substance drilled, as described in Israel patent application No. 168569. 
     In addition, by continuously measuring the coil ohmic resistance (the instant ratio between the voltage develops on the coil and the current fed through the coil, one can deduct the ambient temperature surrounding the coils. This is based on the physical characteristic of the coil material, where its resistance depends on its temperature. This continuous measurement of the temperature, may also be used for providing an alert to the practitioner and/or for performing an automatic shut off of the active vibrations, whenever too high temperature is reached, and thereafter resuming the vibrations, when the ambient temperature surrounding the coils falls down to a safe level. 
     Alternatively or additionally, the vibration of the drilling guidewire may be achieved by other means, such as by providing a constant distally directed force on magnetic coupling means mounted on a distal end section of the drilling guidewire, and concurrently applying alternating proximally directed force, by externally (manually or mechanically) pulling the guidewire. In this way a longitudinal and possibly also a transverse vibrating mechanism is achieved. 
     Alternatively or additionally, the vibrations of the drilling guidewire may be achieved by clamping the guidewire within a catheter, while vibrating said catheter. More specifically, it may be excited, by using a catheter comprising at least two conduits, e.g., an inner conduit disposed within an outer conduit. The inner conduit, such as in a balloon catheter accurately matches the guidewire diameter. Magnets, preferably miniature in size and radial in shape are attached to the wall of the inner conduit, or are embedded therein. The outer conduit of the catheter is enwrapped or embedded in a coil, preferably several coils. The inner conduit is relatively free within the outer conduit, and hence by feeding an alternating current through the coils, an alternating magnetic force develops, vibrating the inner conduit of the catheter, and hence vibrating the guidewire clamped within the lumen of said inner conduit. Alternatively, the catheter device may be operated without the guidewire by using the distal end of the inner conduit as a drilling head. 
     Additionally or alternatively the inner magnets may be arranged non-radially, such that the generated vibrations may progress both, in longitudinal as well as in transverse directions. 
     Alternatively or additionally, the distal drilling tip of the guidewire is provided with bending piezo actuators, such that, by controlling the electrical current fed into the actuator, the guidewire tip can be vibrated and/or directed into a desired direction in vivo. 
     The present invention also provides means for in vivo sensing the tissue/substance with which the device of the invention is in contact or in proximity with by means of one or more acoustic transducers (e.g., Piezo electric transducers) and/or provides means for analyzing the magnetic impedance of one or more electric coils that are fed by an electrical alternating current. These transducers and or coils are held in proximity to living tissues affecting the acoustic and or magnetic impedance of the volume in the vicinity of the transducers and or coils. Changes in the acoustic and/or magnetic impedance results in changes in the voltage and current vs. frequency driving the transducers and/or coils. These changes can be measured by the driver of the transducers and/or coils, that may be remotely positioned away from the transducers and/or coils themselves, i.e. outside the body. 
     In one preferred embodiment of the invention the device is equipped with miniature magnets mounted and/or embedded near the distal tip of a guidewire. These magnets are activated when said guidewire is threaded through electrical coils fed with an electrical current. This guidewire, when threaded into body passageways or organs, can “feel” the different magnetic impedance surrounding its tip, as the guidewire is passed through said passageways and/or organ by the practitioner. In this embodiment, the driving unit of the coils is located remotely from the coils themselves. 
     The magnetic impedance of the coils is preferably measured at the driving unit end (proximal end) of the catheter. This measurement may be carried out by continuously measuring the electrical voltage over the coils and dividing the same by the value of the electrical current driving said coils. The magnetic impedance may be measured at different frequencies, thus providing a more comprehensive result of magnetic impedance at different frequencies. For this purpose the driving unit may be equipped with analog to digital converters and a processing unit for converting the values of the measured electrical voltage and driving current and computing the magnetic impedance by dividing the digital representation of the measured electrical voltage by the digital representation of the driving current. 
     The measured impedances may be used to characterize the tissue/substance that is in contact with, or in proximity to, the guidewire distal tip and thereby to provide clinical indications (e.g., to distinguish between plaque, blood, vessel walls or any other tissue that may be in the proximity of the tip of the guidewire), thus making it possible for the practitioner to distinguish between the plaque build-up inside the artery and the vessel walls (intima, media or adventitia). 
     In another embodiment of the invention the device of the invention is equipped with miniature acoustic transducers mounted at the distal tip of a guidewire. This guidewire, when threaded into body passageways, can “feel” the different acoustical impedance surrounding the transducers, as the guidewire is passed through the said passageways by the practitioner. In this embodiment, the driving unit of the transducers is located distantly from the transducers themselves. The acoustic impedance is preferably measured at the driving unit end (proximal end) of the guidewire. The measured impedances may be used to characterize the tissue/substance being in contact with the guidewire distal tip and thereby to provide clinical indications (e.g., allow to distinguish between plaque, blood, vessel walls or any other tissue that may be in the proximity of the tip of the guidewire), thus making it possible for the practitioner to distinguish between the plaque build-up inside the artery and the vessel walls (media). 
     Additionally or alternatively, the device of the invention includes electrically vibratable means, such as an ultrasound transducer, embedded in the distal end of the drilling guidewire and/or in the catheter distal end, thereby allowing vibrating the distal end of the device at an ultrasonic frequency (controlled and regulated from a control unit connected to the proximal end of the unit in vitro) for drilling through the occlusion. The electrically vibratable means preferably comprises a micro piezoelectric device capable of efficiently transferring energy to hard/calcified tissues and thus allows destruction of plaque rather than of the elastic passageway wall. 
     The drilling effect of the device of the present invention is achieved by two main mechanisms: i) the direct rapid mechanical vibrations applied into the occlusion, or ii) by cavitation effect, in which the ultrasonic waves in the blood produce tiny bubbles, forming a fractal structure and radiating sound by themselves. The cavitation field that is being produced by a radially symmetric sound field burst of approximately 23 kHz onto the occlusion at high energy, thus damaging and/or breaking up the plaque. 
     The catheter device of the invention may be implemented using a low diameter catheter tube which includes a magnetic guidewire centering means surrounding the guidewire. This magnetic guidewire centering means uses unidirectional magnetic forces that force a guidewire comprising a magnetic element to float inside the catheter due to repulsion of magnetic forces evolving between said magnetic element and said magnetic guidewire centering means, thus stabilizing the guidewire (ensuring the guidewire will vibrate in a controlled direction and will not deviate in undesirable directions) thereby reducing friction and improving guidewire rotational movement abilities. This magnetic centering means may be either passive, i.e. comprising permanent magnets, or active, i.e. comprising a combination of permanent magnets and electromagnetic coil. 
     The device of the invention may further include a lumen for debris aspiration, and it may be further adapted to allow injection of fluids via the guidewire lumen, such as contrast media and/or cooled saline for temperature control. 
     The invention also provides a means for deflecting the driller tip into a desired in vivo direction thereby imparting additional maneuverability to the distal tip of the guidewire, when passing through complicated artery morphologies. 
     The catheter device of the invention may be equipped with a thermo-sensor mounted in the distal end of the catheter that is used to communicate temperature readings to the practitioner either via wires or wirelessly, from the distal end of the catheter to the proximal end. 
     The proximal end of the catheter device of the invention may be bifurcated to provide a first entrance for the drilling/sensing guidewire and an entrance for saline/contrast media or other fluid, the debris aspiration tube, the ultrasound transducer power cords and the thermo-sensor power/reading cords, if any. 
     The present invention also provides a method for opening occluded body passageways by means of a drilling guidewire, which may be a conventional guidewire that is slightly modified and which may be operated (upon physician selection) in an active mode (electrically powered) as a driller held by the catheter surrounding the guidewire near its distal end. Thereby, the physician can advance the guidewire as far as possible towards the occlusion while the device is in a passive mode, and upon reaching an occluded section switching the device into an active mode, thereby initiating a drilling process to allow further advancing the guidewire all the way to the distal end of the occlusion, and thereafter to treat the occluded passageways using conventional procedures, such as by means of balloon catheters and/or stents. 
     The Apparatus 
     The present invention is directed to an active guidewire housed in a magnetic catheter based device, to a method for opening obstructed body internal passages and for sensing and characterizing tissues and substances being in contact with the device of the invention. 
     In general, the device of the present invention comprises a coiled guide wire, capable of inducing magnetic force(s) therein while threaded through a catheter with fixed magnets attached to it. That magnetic force can be an alternating magnetic force, creating vibrations in the tip of the guidewire, wherein said vibrations of the guidewire are utilized for opening a passage through an occlusion. 
     An alternative apparatus comprises coiled guide wire threaded into a human vessel, which is positioned in a strong magnetic gradient flux. This magnetic gradient flux is generated by in-vitro magnetic apparatuses&#39;, such as strong fix magnets, or strong electro-magnets. 
     More particularly, the present invention relates to a device and method for in vivo drilling in living tissue and/or finding the weak path in the said living tissue, in body internal passages and body organs, which may be utilized for opening a passage suitable for passing a treatment device (e.g., a stent, balloon) through an occluded body internal passage (e.g., blood vessel), such as in cases of CTO. The in vivo drilling is performed by means of a drilling guidewire with an embedded electro-magnet, and more specifically a coil based electro-magnet section that aside from drilling through the occlusion enables the operator to sense the tissue/substance being in contact with the drilling part of the drilling guidewire. The sensing of the tissue/substance contacting the drilling guidewire may be advantageously used to provide an indication as to whether the drilling guidewire properly operates in the occluded internal passage or whether it deviates therefrom and injures the passage wall. The path drilled and or opened and or re-canalized through the occluding matter enables the passage of an either the special guidewire or another conventional guidewire through the occluded passage and thereby allows carrying out the conventional treatments of “over-the wire” applicable in such cases, such as, for example, by means of balloon catheters and stents. 
     The drilling according to this invention is based on an electro-magnetic force generated by the combination of feeding current through a guidewire according to the invention, threaded in a catheter with embedded magnets. The drilling itself is carried out by means of rapid vibrations e.g., at a frequency of about several dozens Hz, preferably in the region of 1-600 Hz, low amplitude vibrations e.g., with an amplitude of about a fraction of a mm, preferably in the region of 0.01 to 1 mm, that are directed in vivo to the occluding matter. The in vivo drilling device of the invention is designed to transfer the drilling energy with high efficiency into hard/calcified tissue, while keeping the efficiency low when drilling into relatively soft tissues. The drilling vibrations are preferably limited to low amplitudes, resulting in a drilling scheme that transfers energy very efficiently into hard/calcified occlusions. At the same time, such drilling cannot transfer energy efficiently into soft tissues, such as the artery wall, thus lowering the risk of perforation or dissection thereof. 
     The present invention also provides a method for opening occluded body passageways by means of a drilling guidewire, which comprises a conventional guidewire that is slightly modified and which is operated (upon physician selection) in an active mode (electrically powered) as a driller held by the catheter surrounding the guidewire near its distal end. In this manner the physician can advance the guidewire as far as possible towards the occlusion while the device is in a passive mode, and upon reaching an occluded section the physician switches the device into an active mode, thereby initiating an active magnetic drilling process to allow further advancing the of the guidewire all the way to the distal end of the occlusion, and thereafter to treat the occluded passageways using conventional procedures, such as by means of balloon catheters and/or stents. 
     The Guide Wire 
     A preferred guidewire according to the invention is based on a conventional configuration guidewire with the added capability of driving an electrical current through the coils that are a part of the guidewire. 
     In another embodiment of the invention, the coil already embedded in a conventional guidewire is electrically connected to an external current driving unit, thus creating a magnetic flux in the vicinity of said coil. When the coil is then inserted into a magnetic field gradient, an induced magnetic force is developed which acts on the coil. This magnetic field gradient may be generated either by in-vivo means, or by ex-vivo (external to the human body) means. 
     In yet another embodiment of this invention, the coils that are electrically connected to an external current driving unit are positioned at various places along the guidewire. 
     In a preferred embodiment of the invention, the coil is positioned at the front portion of the guidewire (i.e. in the region of its distal end). The exact position of the coil may vary from one embodiment to another. 
     In a further embodiment of the invention, the coil distal end is positioned approximately 50 mm before the distal tip of the guidewire. 
     In yet another embodiment of this invention, the coil distal end is positioned just at the tip of said guidewire. 
     In yet alternative embodiments of this invention, the coil distal end may be positioned along the guidewire at any distance, in the range of 10-300 mm away from the distal tip of the guidewire. 
     In yet another preferred embodiment of the invention, the coil may be divided into several gapped segments of coils, implemented in an optimized electro-magnet configuration to achieve a significant magnetic field flux along the guidewire. 
     In yet another preferred embodiment of the invention, the number of divided coil segments is typically in the range of 3 to 30. 
     All such segments can be connected in serial to each other, or in another electrical connection, which allows achieving the desired result. 
     In yet another preferred embodiment of the invention, the coils are connected in serial to each other in such a manner that the current direction changes from one coil to its neighboring coil. In short, assuming there are e.g. 7 coils, then all coils are connected in serial to each other, in a way that the current fed into coils  1 ,  3 ,  5  and  7  flows in “clockwise” direction, while the current fed into coils  2 ,  4  and  6  flows in “counterclockwise” direction. 
     In yet another preferred embodiment of this invention, the gap between adjacent coils will be of the order of 1-5 mm, while the length of each coil section may preferably be in the range of 0.5-10 mm. 
     In yet another preferred embodiment of this invention, the gaps between the coils section may be one of the following:
         Left empty.   Filled with another passive coil, that is not connected to an electrical driving unit.   Filled with other material, preferably a bio-compatible type of material.   Filled with a thermal conductive material, to sink the heat dissipation generated by the coil into the metal inner member of the guidewire.       

     In yet another preferred embodiment of the invention, the coils are made of wire with diameter that is in the range of 25 to 100 microns (1 to 4 mils). 
     The coils are made of silver, copper, platinum, or any other material that is compatible for inserting into living organs of a human being. 
     In yet another preferred embodiment of the invention, the coil may be of a mechanical structure similar or identical to the mechanical structure already implemented in the guidewire, hence suitable for use in catheterization and/or treatment of live human beings. 
     In yet another preferred embodiment of the invention, the external diameter of the coil(s) is identical to the external diameter of the guidewire section, in which the coil(s) are embedded, typically in the range of 14 to 18 mils. 
     In yet another preferred embodiment of this invention, the coils are coated with isolating materials. Preferably these materials will provide clinical benefits, such as hydrophilic coating. 
     In yet another preferred embodiment of this invention, the coating may be of bio-compatible type, such as a Teflon based coating i.e., a polytetrafluoroethylene (PTFE) based coating. 
     In yet another preferred embodiment of this invention, the coils are connected to an external current driving unit, by means of two leads that are pulled along the guidewire up to its proximal side end. Optionally these leads can be threaded alongside the guidewire, wrapped in an isolating shrinkable sleeve, or through a hollow core of the guidewire. Alternatively, either of the leads can be a part of the core member of the proximal portion of the guidewire. It should also mentioned, that more than a single lead can be a part of the core member of the proximal portion of the guidewire, assuming it is designed in a way to be comprised of several electrically isolated cores aligned with each other. In this embodiment the leads are optionally terminated with a connector, preferably miniature connector, or as bare wires, directly connected to the external driving unit. 
     The present invention also provides a guidewire device, capable of electrically controlling its distal tip pushing force, according to the electrical current fed into the coils of the guidewire. 
     An oscillating current will result in an oscillating magnetic force, the magnitude of the force depending on the amplitude of the current fed. 
     A DC current will result in a constant magnetic force, which adds to the inherent mechanical force of the tip of the guidewire, hence changing its stiffness according to the current level. 
     The Catheter 
     The in vivo drilling of the guidewire according to the invention is achieved when threading the guidewire according to the invention into a magnetic catheter, and then feeding electrical current into the coils of the guidewire. 
     The catheter according to this invention may be any type of hollow tube. 
     Preferably, the hollow tube may be made for clinical use in general, and more particularly for use in coronary catheterization procedures. 
     In yet another preferred embodiment of the invention, the catheter is a conventional catheter provided with magnetic beads along it. 
     In yet another preferred embodiment of the invention, the magnetic beads are hollow beads, attached to the inner wall, the outer wall, or embedded in the wall of the catheter. 
     In yet another preferred embodiment of the invention, the magnetic beads are made of rare earth magnets, such as NdFeB grade 48. The preferred size of the said magnetic beads is preferably designed to match the design of the coils of the guidewire. 
     In an optional embodiment of the catheter according to the invention, the number of magnetic beads along a specific length of catheter equals the number of coil segments along same length of the guidewire. 
     Alternatively, the number of coils can differ from the number of magnetic beads. In this case the maximum magnetic force generated by the apparatus shall be maintained as long as coils are surrounded by magnetic beads. 
     In a preferred embodiment of the invention, each coil segment of the guidewire is surrounded by two magnetic beads attached to a catheter, in a manner that the magnetic field generated by the coil is positioned in a high gradient of the magnetic field generated by the two beads, hence producing a magnetic force. 
     In yet another preferred embodiment of the invention, the magnetic bead may be a hollow shaped cylinder, with outer diameter of 2.7 F(0.9 mm) and an inner hole diameter of 2.0 F (0.65 mm) with a length of 3 mm. 
     The frequency of the vibrations may be changed in close loop in order to manually or automatically reach the resonance frequency or anti-resonance of the whole apparatus, thus gaining continuous optimization of the drilling energy. 
     In yet another embodiment of the catheter according to the invention, the rare earth magnets of the catheter can act also as radio opaque markers, used for identification (automatically and/or manually) of the relative position between the guidewire and the catheter, and hence provide means to selectively drive coils that are overlapping the guidewire magnets. Such selective driving provides the following main advantages: 
     The power loss on the coils is lower relative to the power loss when activating all the coils (as only some of the coils are driven). 
     The working range of the magnetic force may be increased, relative to the working range when powering all of the coils. 
     The magnetic force level may be efficiently developed, as only coils that contribute to the magnetic power are activated, while other coils are selectively not powered. 
     Sensing 
     The electrical power (current and voltage vs. frequency) fed into the vibrating elements, can be analyzed to measure the overall apparatus magnetic impedance, and thereby provide an indication about the type of tissue/substance drilled, as described in Israel copending patent application No. 168569 and in copending application PCT12006/000541. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
       The present invention is illustrated by way of example in the accompanying drawings, in which similar references consistently indicate similar elements and in which: 
         FIG. 1A  shows a longitudinal and a cross-sectional view of a catheter device of the invention for opening occluded passageways by means of a vibrated magnetic field; 
         FIG. 1B  illustrates a possible arrangement of magnets and electrically vibratable means; 
         FIG. 1C  illustrates a catheter device of the invention for opening occluded passageways by mechanically induced vibrations and magnetic attraction forces; 
         FIG. 1D  shows a possible guidewire structure of the invention having an embedded ferromagnetic section; 
         FIG. 2A  illustrates a catheter device of the invention for opening occluded passageways by means of a magnetic field induced by a coil; 
         FIG. 2B  illustrates a catheter device of the invention for opening occluded passageways by means of a magnetic field induced by a plurality of coils; 
         FIG. 2C  illustrates a catheter device of the invention for opening occluded passageways by means of a magnetic field induced by a plurality of coils separately energized by a power source; 
         FIG. 2D  shows a possible electrical activation scheme of the separate coils arrangement shown in  FIG. 2C ; 
         FIG. 3A  shows a longitudinal and a cross-sectional view of a catheter device of the invention for opening occluded passageways by means of an electrical vibratable element; 
         FIG. 3B  shows a longitudinal and a cross-sectional view of another embodiment of the catheter device of the invention for opening occluded passageways by means of an electrical vibratable element; 
         FIG. 4A  illustrates a catheter device of the invention capable of centering a guidewire passing therein by means of fixed magnets; 
         FIG. 4B  illustrates a catheter device of the invention capable of centering a guidewire passing therein by means of a fixed magnet and an electromagnetic coil; 
         FIG. 5A  illustrates a guidewire of the invention comprising an acoustic impedance sensing means; 
         FIG. 5B  illustrates a possible acoustic head arrangement of the invention; 
         FIG. 5C  illustrates a possible structure of an acoustic transducer comprising a waveguide; 
         FIG. 5D  exemplifies various signals that may be obtained via acoustic impedance sensing means; and 
         FIG. 5E  schematically exemplifies the operation of an acoustic transducer of the invention. 
         FIG. 6  illustrates a longitudinal view of another embodiment of the catheter device of the invention which is comprised of an outer conduit comprising an inner conduit, wherein a guidewire is threaded through the lumen of the inner conduit which is surrounded by miniature magnets, and wherein coils are wrapped around the outer conduit of the catheter. 
         FIG. 7  shows the general structure a prior art guidewire, 
         FIG. 8  shows a general structure of a prior art catheter, 
         FIGS. 9A and 9B  show a general typically usage of the prior art guidewire, when threaded for clinical treatment through a prior art catheter, 
         FIGS. 10A ,  10 B,  10 C and  10 D show a preferred guidewire embodiment according to the invention, 
         FIG. 11A  shows a close up cross-sectional look of the coils according to the invention, and  FIG. 11B  the magnetic flux developed thereby, 
         FIGS. 12A and 12B  show other configurations of the guidewire, 
         FIGS. 13A and 13B  show the catheter according to the invention with magnetic beads, 
         FIGS. 13C and 13D  show a typical magnetic field developed by the magnetic beads, 
         FIGS. 14A and 14B  show a use of the guidewire when threaded via the catheter, to enable the desirable active drilling of the apparatus, 
         FIG. 15  shows another drilling apparatus based on the guidewire and the catheter, 
         FIG. 16  shows the leads connecting the guidewire to the external current driver, and 
         FIG. 17  shows a schematic block diagram of an external driver unit. 
     
    
    
     DETAILED DESCRIPTION OF PREFERRED EMBODIMENTS 
       FIG. 1  shows longitudinal and cross-sectional views of a device  201  designed for in vivo generating and transferring mechanical vibrations. The device  201  comprises a catheter tube  204  and a drilling guidewire  202  passing therethrough. Drilling guidewire  202  comprises miniature magnets  203  radially attached thereto near its distal tip. Catheter tube  204 , comprising guidewire  202 , comprises magnetic field inducing means  205  attached to the inner wall of catheter tube  204  near its distal end opening  204   b . Magnetic field inducing means  205  may also be embedded in the wall of catheter tube  204  (not shown). In this preferred embodiment magnetic field inducing means  205  are implemented by a structure comprising fixed magnets,  205   a  and  205   b , and vibratable (e.g., piezoelectric) elements  206 , attaching the fixed magnets. Vibratable elements  206  are supplied with electrical power E(t) provided by electrical power source  208  via electrical wiring  207 . Drilling guidewire  202  comprises magnetic coupling means implemented by miniature magnets  203  mounted near a distal end portion thereof. 
     Fixed magnets,  205   a  and  205   b , and vibratable elements  206  are preferably hollow cylindrical elements configured to allow passage of a guidewire therethrough. Alternatively they may be embedded within guidewire  202 . When operated in a drilling mode, an alternating electrical signal is supplied to vibratable elements  206  which in turn vibrate fixed magnets  205   a  and  205   b , thereby inducing a vibrating magnetic field in the proximal end portion of catheter tube  204 . Miniature magnets  203  are affixed near a distal end section of guidewire  202  such that when said distal end section of guidewire  202  is positioned within the structure comprising fixed magnets,  205   a  and  205   b , and vibratable (e.g., piezoelectric) elements  206 , a distal end portion of guidewire  202  protrudes outwardly via the distal end opening of catheter tube  204 . 
     The structure comprising fixed magnets,  205   a  and  205   b , and vibratable elements  206 , connecting said fixed magnets may be attached to the inner wall of catheter tube  204  via magnet  205   b , such that magnet  205   a  connected thereto via vibratable element  206  is maintained in the interior of the catheter in a more or less floating state, as exemplified in  FIG. 1A . Alternatively, vibratable elements  206  may be attached to the outer wall of catheter tube  204 , or be embedded therein (not shown). In a similar fashion additional magnets  205   a  may be attached by means of vibratable elements  206   a ,  206   b  and  206   c , connected therebetween, to provide a structure of “floating” magnets  205   a  connected to magnet  205   b , which is affixed to the inner wall of catheter tube  204 , as exemplified in  FIG. 1B . Similarly, said structure containing “floating” magnets  205   a  is free to vibrate in the guidewire lumen of catheter tube  204 . 
     Guidewire  202  may be a conventional guidewire such as the Cordis Wizdom guidewire (Johnson &amp; Johnson, USA), or more preferably may be a guidewire having medium distal stiffness, specially designed for treatment of CTOs such as the Pilot 50 manufactured by Guidant, USA. Miniature magnets  203 , can be manufactured from rare earth materials such as NdFeb series, preferably from NdFeB grade 42 or higher, and they are preferably in the shape of miniature hollow cylinders attached to the guidewire  202 , as shown in the cross-sectional view in  FIG. 1A , or are embedded within the guidewire (not shown). The outer diameter of the magnets  203  should be configured according to the diameter of guidewire  202 , for example, if the diameter of guidewire  202  is about 0.36 mm (14 mils), then the outer diameter of miniature magnets  203  may generally be in the range of 0.5 to 1.0 mm, preferably about 0.7 mm, while their inner diameter should match the guidewire diameter or will be reduced down to zero in the case they are embedded in the wire. The thickness of the miniature magnets  203  can vary and reach several mm, all in accordance to the guidewire they are attached to and or embedded within. For example, the length of miniature magnets  203  may generally be in the range of 1.0 to 5.0 mm, preferably about 2.5-3.0 mm. 
     The distal end portion of guidewire  202  is preferably made of a material that is softer or less stiff, in relation to the other portions thereof in order to allow it to collapse and in this way to avoid any possible damage, such as perforation or dissection to the arteries wall. Miniature magnets  203  are preferably affixed on a distal section of guidewire  202 , near its distal end portion. While in the above examples, and in the figures, miniature magnets  203  and guidewire  202  are concentric, and the intervals between miniature magnets  203  are of equal length, the invention may also advantageously utilize different configurations. For example, miniature magnets  203  may be mounted on guidewire  202  in a non-concentric form and the interval between miniature magnets  203  may be of different lengths. 
     Similarly, the geometrical dimensions of fixed magnets,  205   a  and  205   b , and vibratable elements  206  should be adjusted according to the inner radius of catheter tube  204 . For example, if the inner diameter of catheter tube  204  is about 1.0 mm, then the inner diameter of fixed magnets,  205   a  and  205   b , may generally be in the range of 0.7 to 0.9 mm, preferably about 0.8 mm. Fixed magnets,  205   a  and  205   b , can be manufactured from rare earth materials such as NdFeB series, preferably from NdFeB grade 42 or higher, and vibratable elements  206  is preferably a type of piezoelectric element such as manufactured by APC. 
     By applying voltage of the order of several dozens of Volts to the opposite ends of the piezoelectric element, said element bends and straightens at an amplitude of a fraction of a mm, hence changing the magnetic field surrounding the magnets attached to guidewire  202 . This change in the magnetic field causes evolution of a magnetic force of the order of up to several grams. 
       FIG. 1C  is a longitudinal view of a device  211  of the invention in which the proximal end of guidewire  220  is held by mechanical means  221 , capable of repeatedly applying rapid longitudinal pulling forces (designated by arrow  224 ) thereto. Mechanical means  221  may be implemented by several methods, for example by connecting guidewire  220  to an external vibratable element, such a piezoelectric transducer, activated by a suitable electrical powering signal. Catheter tube  222  includes a series of fixed magnets  223   a ,  223   b ,  223   c , . . . , affixed to (or alternatively embedded in, not shown) the inner wall of catheter tube  222 . Internal magnets  223   a ,  223   b ,  223   c , . . . , are preferably hollow cylindrical magnets configured to apply distally pulling forces (designated by arrow  225 —pulling towards the distal end of the guidewire) on miniature magnet  203  affixed to (or embedded in, not shown) guidewire  220 . External mechanical means  221  applies repeated rapid pulling force  224  which due to the distal attraction applied by fixed magnets  223   a ,  223   b ,  223   c , . . . , results in rapid longitudinal vibrations of the distal tip of the guidewire  220 . 
     Fixed magnets  223   a ,  223   b ,  223   c , . . . , can be manufactured from rare earth materials such as NdFeB, preferably from NdFeB grade 42 or higher. The outer diameter of fixed magnets  223   a ,  223   b ,  223   c , . . . , should be set according to the inner diameter of catheter tube  222 . For example, if the inner diameter of catheter device is about 1.0 mm, then the outer diameter of fixed magnets,  223   a ,  223   b ,  223   c , . . . , may generally be in the range of 0.7 to 0.9 mm, preferably about 0.8 mm. 
       FIG. 1D  shows a possible preferred embodiment of a guidewire  234 , which is equipped with a segment  234   a  comprising ferromagnetic and/or magnetic portions  235  embedded therein, thereby creating a ferromagnetic and/or magnetic segment  234   a , which diameter is not larger, or only slightly larger, than the original diameter of the guidewire  234 . This ferromagnetic and/or magnetic segment  234   a , when inserted into a magnetic field gradient is subject to magnetic forces. Of course, the number of ferromagnetic and/or magnetic portions  235  provided in guidewire  234  may be different than that exemplified in  FIG. 1D . 
       FIG. 2A  illustrates a catheter device  210  of the invention which is capable of generating an alternating magnetic field in a lumen thereof by means of an electromagnetic coil  215  wrapped on the inner wall of catheter tube  204 . Alternatively, coil  215  may be externally wrapped on the outer surface of catheter tube  204 , or embedded inside the catheter wall. Coil  215  is preferably located near the distal end opening of catheter tube  204 , and it is activated by an electrical current supplied thereto by means of electrical wires  217  and  218  electrically connecting it to electrical driving unit  213 . Coil  215  is preferably a wrapped wire made from a flexible and electrically conducting material, preferably from copper, and coated with a type of a bio-compatible material, preferably parylene. The diameter of said wrapped wire may be in the range of 0.02 to 0.25 mm, preferably about 0.1 mm. The number of turns of coil  215  may vary according to the implementation specific requirements. For example, in one possible embodiment of the invention the number of turns of coil  215  may be in the range of 30 to 150 turns. The axial length of coil  215  should be adjusted according to the length of the section of guidewire  202  comprising the miniature magnets e.g., about 10 mm. 
       FIG. 2B  illustrates a catheter device  212  of the invention comprising catheter tube  226  equipped with several coils  227 ,  228 ,  229 ,  224 , positioned near its distal end and arranged in a Helmholtz like configuration. Coils  227 ,  228 ,  229 ,  224 , may be wrapped on the inner wall of catheter tube  226 , on its outer surface, or alternatively embedded inside the catheter wall. Guidewire  230  passing in the lumen of catheter tube  226  comprises miniature magnets  231 ,  232 ,  233 , . . . , attached thereto. The location of the coils  227 ,  228 ,  229 ,  224 , and magnets  231 ,  232 ,  233 , . . . , in catheter device  212  is preferably configured to provide segments of adjacently located pairs of coils together with a magnet. For example, coils  227  and  228  may surround magnet  231 , coils  228  and  229  may surrounds magnet  232 , etc. Upon excitation of the coil pairs a gradient of magnetic field is generated in between the coils. When this gradient is generated near the fixed magnets  231 ,  232  and  233  a magnetic force is excited. In the embodiment shown in  FIG. 2B , the current in coils  227  and  229  may be in a clockwise direction, while the current in coils  228  and  224  may be in a counterclockwise direction. The magnets, may then be positioned such that the north poles of magnets  231  and  233  are at the distal side of the magnets, while the north pole of magnet  232  is at the proximal side thereof. Using such an arrangement achieves a multiplication of the magnetic force operating on a single magnet. The multiplication factor is determined by the number of coil/magnet segments. It goes without saying that a different number of coil/magnet segments, other than the three segments shown in the  FIG. 2B , may be employed. 
     For example, an apparatus including 4 coils (3 segments), each having  34  turns, which are being fed with a 1 A electrical current, can produce a force of 3 grams when measured on 3 miniature magnets, the length of which is about 3 mm, and having an outer diameter of about 0.8 mm and an inner diameter of about 0.4 mm. 
       FIGS. 2C and 2D  demonstrates an operation/excitation scheme of a catheter device  212  in which the coils  237   a ,  237   b ,  237   c , . . . , provided in the catheter tube  226  are separately powered via respective wires  238   a ,  238   b ,  238   c , . . . , electrically connecting said coils to an external power source  239 , such that each coil may be operated independently. While it is possible to operate/excite all of the coils  237   a ,  237   b ,  237   c , . . . , that surround the guidewire  230  (not shown in  FIG. 2C ) in phase (meaning the powering electrical current is fed to all coils simultaneously) it is also possible to excite the coils in series one after the other, as exemplified in  FIG. 2D . 
       FIG. 2D  graphically illustrates the currents Ia(t), Ib(t), Ic(t), . . . , supplied to coils  237   a ,  237   b ,  237   c , . . . , respectively in such a possible activation scheme. This activation scheme provides the coils with “wave” like current. The magnetic field is consequently developed in a wave like manner—providing a relatively high duration magnetic field that propagates along the catheter tube  226 . Inserting a guidewire  230  (such as shown in  FIG. 2B ) results in an apparatus that provides relatively constant magnetic force along relatively long range along the catheter/guidewire axis. 
     Additionally, by measuring the coil ohmic resistance (the instant ratio between the voltage developed on the coil and the current fed through the coil), one can deduce the temperature of the ambient surrounding the coils. 
     Advantageously, coils  237   a ,  237   b ,  237   c , . . . , may be designed such that the direction of the activation currents of adjacent coils (e.g., Ia(t) and Ib(t)) are of opposing directions in order to generate magnetic field gradients in the lumen catheter tube  226 . The distances between coils  237   a ,  237   b ,  237   c , . . . , may be of different lengths in order to provide varying distances between the magnetic field gradients. 
     Clearly, other waveforms different than those shown in  FIG. 2D , may be fed into the coils, where the number of coils may again differ from the 3 coils shown in  FIG. 1A . 
       FIG. 3A  shows longitudinal and cross-sectional views of a catheter device  240  comprising a vibratable guidewire  244  designed for in vivo generating and transferring of acoustical (and/or other type of) vibrations. Guidewire  244  passing inside guidewire lumen  242 , comprises an ultrasonic (or another type of) vibrating element  247  that may be used for in vivo inducing vibrations (e.g., acoustic vibrations) and/or for sensing and characterizing the substance/tissue that is in proximity to the distal end of the guidewire device  244 . Guidewire lumen  242  may be also used for injection of liquid, such as cold saline or contrast media. Catheter tube  241  further comprises a debris aspiration lumen  243  and a thermo-sensor  246 . At the proximal end of catheter tube  241 , there are shown power wires  247   w , of the vibrating element  247 , and wires  246   w  connecting to the thermo-sensor  246 . Of course, wires  246   w  are absent when the device according to the invention does not include a thermo-sensor. Wires  246   w  and  247   w  are connected to a control unit  248  capable of inputting thermal readings from thermo-sensor  246 , providing powering signals to vibrating element  247 , and inputting and analyzing signals produced by vibrating element  247 . 
       FIG. 3B  shows longitudinal and cross-sectional views of a catheter device  240   b  comprising a vibratable guidewire  244  designed for in vivo generating and transferring of acoustical and/or other type of vibrations. The operation of catheter device  240   b  is similar to that of catheter device  240 . The structure of catheter device  240   b  is, however, different in that the guidewire lumen  242   b  is concentrically located in the debris aspiration lumen  243   b.    
       FIG. 4A  illustrates a possible arrangement for a catheter device  265  capable of centering a guidewire  261  passing therethrough by means of fixed magnets,  260  and  262 . Fixed magnet  260  is preferably a hollow cylindrical magnet attached to the inner wall of catheter tube  263  (or embedded in it, not shown), such that guidewire  261  can be freely moved longitudinally therethrough. Fixed magnet  262  is affixed to guidewire  261  at a location corresponding to the location of fixed magnet  262  in catheter tube  263 . Fixed magnets  260  and  262  are designed such that repulsion forces caused due to their opposite magnetic polarities centers guidewire  261  inside catheter tube  263  when positioned therein in its operative state, as exemplified in  FIG. 4A . In similar way, in  FIG. 4B  guidewire  261  is centered inside catheter tube  263  by means of electromagnetic coil  265 . Coil  265  may be activated once guidewire  261  is positioned in an operative state in catheter tube  263  by supplying it electrical current via conducting wires electrically connected to it. 
       FIG. 5A  shows a conventional guidewire  252  comprising one or more miniature acoustic and/or other transducers  256  which are fed with electrical power provided by electronic unit driver  253  electrically connected thereto by means of electrical wires  254 . Electronic unit driver  253  is advantageously designed to provide various electrical supply signals, in particular it may be able to supply direct current (DC) and alternating current (AC) in high frequencies. 
       FIG. 5B  shows a preferred embodiment of the acoustic or other transducer  257  of guidewire  252 . Acoustic or other transducer  257  comprises an active part  250 , such as a piezoelectric module, which is fed via wires  254  electrically attached thereto. Active part  250  is packed in an acoustic\vibrating head  251 . Head  251  can provide readings that may be used to characterize tissue/substance  258  which it is acoustically or physically touching, and/or which is in its proximity. The design and construction of acoustic head  251  may vary from one embodiment to another, depending on the tissue/substance  258  in proximity thereto. 
       FIG. 5C  shows another embodiment of a transducer (e.g., acoustic transducer) of the invention in which the active part  250  (that may be a piezoelectric transducer) is coupled to head  251  (e.g., acoustic head), via a waveguide  259  (e.g., acoustic waveguide). Conducting wires  254  are used to provide electrical supply to active part  250 , and to output signals read from active part  250  that may be used to characterize tissue/substance  258  with which it is in contact, or in its proximity. It should be mentioned that waveguide  259 , may carry both longitudinal waves, and/or transverse waves or both, and it may be built either in hollow configuration or solid one, with different lengths as implied by the specific implementation of this embodiment. Guidewire  252  may be a conventional cardiac coronary guidewire as commonly used in coronary catheterization procedures. 
     When the guidewire reaches a lesion difficult to pass, the sensing tip is activated and transmits acoustic or vibrating energy into the problematic lesion. The impedance of that lesion is relative to the type of occlusion reached. Thus the practitioner can determine whether he reached a healthy part of the artery (touching the vessel wall for instance) or a diseased portion, i.e. a calcified/fibrotic and/or other type of occlusion. 
     The interpretation of the occlusion reached is done by remotely analyzing the acoustic impedance of the material that is in proximity to the guidewire tip. A schematic reading for that acoustic impedance is shown roughly in  FIG. 5D . Items  276 ,  277  and  278  represent acoustic impedances of different substances/tissues that were measured in proximity to the guidewire tip. 
       FIG. 5E  illustrates the physical mechanism of the acoustic transducer of the invention. In any embodiment used, and under certain physical estimations, the behavior of the acoustic transducer, and its interaction with the substance/tissue it is in proximity with is as illustrated in  FIG. 5E . 
     The left side, designated by numeral  260 , is the electrical equivalent of the acoustic transducer. It comprises an electronic unit driver  263  connected to the acoustic transducer. The electrical characteristics of the acoustic transducer are described by an LC circuit,  267  and left part of transformer  268 . 
     The transformation of the electrical energy into the mechanical movement/energy of the transducer (that then creates acoustic energy) is effected by transformer coupling  268 . The right side of transformer  268  provides the energy to activate the acoustic transducer. In the case of most acoustic transducers, and specifically in piezoelectric type transducers, the energy is fed into them is converted into mechanical movements. Parts  269  and  261  represent the construction of the transducer itself. 
     A capacitor  289 , connected in series with inductor  281 , provides a simple apparatus, with a single resonance frequency. This representation can then be used to represent an acoustic transducer up to the first resonance (but it gives a simple illustration to the physical mechanism). In the acoustic domain, the velocity and the force which represent the mechanical characteristics of the transducer correspond to the current and voltage, respectively of capacitor  289  and inductor  281 . 
     Since there is always loss of energy, the device includes resistor  284 . The interaction of the acoustic transducer with the tissue sensed is represented by  282 . 
     When the transducer apparatus is operated, it receives the activating energy from the electronic unit driver  283 , and in response it mechanically moves parts  289  and  81  which create an acoustic energy, some of which is transferred to resistor  84 , while the rest penetrates into the tissue  282 . 
     The “load” induced by the tissue (the equivalent acoustic load of  282 ) influences the behavior of the system. It actually changes the relationship between the velocity and power of the acoustic transducer, which is correlated to the voltage and current of the driver. 
     It is then possible to measure the electrical impedance (ratio between voltage and current) at the left side of the apparatus  280 , and estimate the acoustic impedance of the right side  286 . 
     Again, the acoustic impedance depends on the mechanical characteristics of the acoustic transducer (parts  289  and  281 ), the efficiency of the acoustic process  284  and the acoustic characteristics of the tissue  282  which is in proximity to the transducer. Thus, by estimating the acoustic impedance of the apparatus, it is possible to derive the acoustic characteristics of the tissue to sense. 
     It should also be mentioned that other equivalent schemes for apparatus containing acoustical transducers may be used. Some of those alternative schemes may be found in the existing technical literature, for example in “introduction to Theory and Design of Sonar Transducer”, written by Oscar Bryan Wilson and published by Peninsula Publishing, Los Altos Calif., USA—1985. 
       FIG. 6  shows another embodiment of the invention comprising a catheter device capable of vibrating a conventional guidewire passing therein. In this embodiment the catheter device  298  comprises at least two conduits: An outer conduit  291  and an inner conduit  293 . Guidewire  300  is threaded through the lumen of the inner conduit  293 , and a distal end portion thereof emerges via the distal end opening of outer conduit  291  of catheter device  298 . 
     Several magnets  290 ,  304  and  306  are attached around the outer surface of inner conduit  293 . The length of magnets  290 ,  304  and  306  may be in the range of 1.0 to 5.0 mm. Magnets  290 ,  304  and  306  may have a hollow cylindrical shape having an outer diameter in the range of 0.5 to 1.5 mm, and an inner diameter that matches the outer diameter of conduit  293 . Coils  292 ,  294 ,  295  and  296 , wrapped over the outer surface of outer conduit  291 , are made from a type of electrically conducting material, preferably from a copper wire coated with a bio-compatible material, preferably parylene, wherein the wire diameter is in the range of 0.05 to 0.25 mm. 
     The diameter of the inner conduit  293  of catheter  298  is designed to tightly fit over the outer surface of guidewire  300 , thereby forcing guidewire  300  to axially move distally and proximally in a longitudinal direction. The diameter of inner conduit  293  may generally be in the range of 0.4 to 0.6 mm. 
     When activating coils  292 ,  294 ,  295  and  296  via an external driver  302 , a magnetic field is induced, which in effect introduce a magnetic force acting on magnets  290 ,  304  and  306 . Alternating the current fed into these coils results in alternating the magnetic force acting on the magnets, which in turn results in vibrations of inner conduit  293  relative to outer conduit  291  of catheter  298 . Since the inner conduit  293  clamps guidewire  300 , guidewire  300  is forced to vibrate as well. 
     While in the example shown in  FIG. 6  coils  292 ,  294 ,  295  and  296 , are wrapped externally (on the outer surface of outer conduit  291 ), they may as well be wrapped internally on the inner wall of outer conduit  291 , or embedded in its wall. Similarly, magnets  290 ,  304  and  306  may be embedded into the wall of inner conduit  293 . 
       FIG. 7  shows a typical prior art guidewire. Generally speaking the guidewire is divided into 2 main zones, a working zone  8 , that are inserted into a vessel in the human body during a typical procedure carried out by a practitioner and the rest of the guidewire  10 , which in most cases does not touch the vessel walls, as it is typically housed in a catheter. The overall length of typical guidewires varies in the range of about 160 to 300 cm. The working zone  8 , is divided into several segments. The front tip  2  of the guidewire, is the first part of the guidewire that touches the organ, and must be designed in a way so as to not harm the organ or vessel wall. A first core member  4 , follows the distal tip of the guidewire, surrounded by a spring type envelope  12 . The section that contains the core member  4 , typically sets the flexible zone of the guidewire enabling it to propagate safely and conveniently through the vessel. A thicker second core member  6 , follows the first core member  4 , forming a less flexible zone also called “stent zone”. Second core member  6  is connected to a third core member, which is thicker and stronger and is used to enable the pushing of the guidewire along the vessel. Some guidewires may include different numbers of zones than described in this figure, e.g. to fit special clinical needs, yet this description gives a comprehensive structure of a typical guidewire. All core members are sometimes surrounded by spring type coils  12 . The spring type coils  12  cover is may in some cases be coated with special coatings, such as hydrophilic coating  14 . 
       FIG. 8  shows a typical structure of a prior art catheter  16 . The catheter  16  in a typical case forms a hollow plastic tube, capable of being inserted into human arteries. This hollow structure enables the transmission of materials, e.g. liquids, and devices, e.g. the guidewire, through its inner lumen. 
       FIGS. 9A and 98  show the typical relation between a guidewire, as shown in  FIG. 7  and a catheter as shown in  FIG. 8 . The guidewire  20  is threaded through a catheter  22 , and then pushed towards the obstructed vessel to enable the treatment. It is typically capable of being to push back and forth guidewire  20  relative to catheter  22 .  FIG. 9B  illustrates that sliding capability, where the guidewire  24  emerges to a significantly greater extent from catheter  26  than is shown in  FIG. 9A . 
       FIG. 10  show a preferred embodiment according to the invention.  FIG. 10A  shows a guidewire  34  having similar sections/zones as a prior art guidewire, however the guidewire includes segmented coils  40  as a part of the overall coil cover  38  of the guidewire  34 . It can be seen that the guidewire is built in a typical structure: A distal tip  30 , followed by a flexible zone core member  32 , followed by a thicker core member  36  (called the “stent zone”), and finally a thicker core member  42 , followed by the rest of the guidewire  44 . The coils covering the different zones, are no longer unified and passive as in the prior art, but rather include several sections  40 , that are electrically connected to each other, and can transmit electrical current, hence generating a magnetic flux. 
       FIG. 10A  shows that the active coil sections  40  cover the core member  42 , containing 5 separate members. 
       FIG. 10B  shows a similar embodiment, however the active coil segments  46  are positioned more distally along the guidewire. The number of the separated segments in this figure is again 5. 
       FIG. 10C  shows another typical embodiment, where the number of active coils sections  48 , is 4. 
       FIG. 10D  shows another typical embodiment, where the active coil sections are not embedded in the passive coil section, as shown in  FIGS. 10A ,  10 B and  10 C, but rather the gaps between the active coils are filled with other types of materials  50 , preferably bio-compatible materials. 
     It is apparent to the man skilled in the art that both, the exact position of the active coils, as well as the number of active coils, may be varied. 
       FIG. 8A  shows a magnified cross section of 5 single layer coil segments. The coils are electrically connected in serial to each other in such a manner so that the direction of the current in coils  60 ,  64  and  68  is clockwise, while the current in coils  62  and  66  is counter clockwise. The resulting magnetic flux vs. the position along the guidewire is schematically shown in  FIG. 8B . Other electrical connections between the coils are may be provided, resulting in different magnetic flux behavior. It is apparent to the man skilled in the art that the number of coils, number of layers for each coil, as well as their electrical connection may be varied. 
     Such configuration may be adapted to the guidewire as shown in  FIG. 10  and  FIG. 12 . 
     Assuming such configuration is indeed adapted to the guidewire shown in  FIG. 10 , it will result in a variable magnetic field along the guidewire section enveloped by the active coils. 
       FIG. 12  shows two additional alternative embodiments for implementing the active coils into the guidewire  74 .  FIG. 12A  shows a configuration where the active coils  72  are formed in a single layer, covered by a passive coil layer  70 .  FIG. 12B  shows active coils segments  76  of two layer each, the gaps between active segments being filled with two layers of passive coils  78 . Dual (or more then single) layers of active coils  76  result in higher (approximately double) magnetic flux generated by the coils, however it also results in s the guidewire to be thicker than if it had only a single layer. 
       FIG. 13  shows a preferred embodiment of a magnetic catheter  80 .  FIG. 13B  shows a hollow cylinder shaped magnet, having a north and south magnetic poles on opposite facets of the cylinder. The magnet bead preferably is made of rare earth magnetic materials such as NdFeB grade 48. A series of such beads, are attached to a catheter as shown in  FIG. 13A . In this figure five beads ( 82 , 84 , 86 , 88  and  90 ), are attached externally to catheter  80 . In this preferred embodiment the direction of the beads is shown schematically in the figure: faces  92 ,  94 ,  96 , and  99  are the south poles of the magnets, while the opposite faces of each magnet is the North Pole. 
     The dependency of the gradient of the magnetic field on the gap between the magnetic beads is shown in  FIGS. 13C and 13D .  FIG. 13C  shows the an apparatus of 2 magnetic beads separated 0.5 mm from each other  83 , the resulting magnetic field is shown in graph  85 . 
       FIG. 13D  shows the magnetic beads  87 , separated 2.0 mm from each other, the resulting magnetic field is shown in graph  89 . These alternatives shown in  FIGS. 13C and 13D , generates a relatively high magnetic field gradient, necessary to generate magnetic force. 
     However it should be emphasized that different number of magnetic beads, other orientation of the magnets as well as other dimensions of the gaps (either equally or not equally gapped) are covered by this invention. 
       FIG. 14  shows a guidewire threaded via the catheter.  FIG. 8A  shows a specific optional positioning of the guidewire  112 , inside the catheter  104 . The maximum magnetic force will be developed once the magnet coil  110  is exactly in between two magnetic beads  100  and  102 . The usage of several magnets, having a certain gap, and several coils having the same period as the magnets, will result in multiplication of the magnetic force accordingly. Other configurations of the magnet/coil arrangement may also be employed. 
       FIG. 14B  shows a different positioning of the guidewire inside the catheter, where coil  129  is overlapped by magnet beads  128  and  120 . 
     In both cases a magnetic force is developed on the active coils of the guidewire. Upon driving the coils with alternating current, the magnetic force is alternating, resulting in longitudinal vibrations of the guidewire and hence the guidewire tip  124 . 
     Theoretically, if the system would be perfectly symmetrical (i.e. the guidewire is exactly in the middle of the catheter), then the magnetic force would be purely in the longitudinal direction. However, as the guidewire is free to move inside the lumen of the catheter, and in most cases the guidewire and the catheter are bent while inserted into human vessel, the configuration deviates from symmetrical, resulting in a magnetic force that also has lateral components. 
       FIG. 15  shows another combination a guidewire and a catheter. In this embodiment a double layered guidewire  142  is threaded via a catheter  140 . The principle of generating magnetic force in this apparatus is similar to that described in  FIGS. 5A and 5B . 
       FIG. 16  shows the leads emerging from the active coils, and strung along the guidewire all the way to its proximal side. In this figure, the active coils are connected in serial to each other, where only two leads  144  and  146  are reach the proximal side of the guidewire. These two leads are then connected to an electrical current driver  148 . When current is driven through the leads, a magnetic field is generated by the coils and induces a magnetic force. There are several possibilities to string the leads from the coils to the proximal guidewire, one being externally to the guidewire itself. A second possibility is to make the guidewire itself hollow inside, enabling the wiring of the leads through this lumen. Alternatively, since in a typical guidewire the core member of the guidewire  147  that follows the coils section  145  of the guidewire, is made of conductive material, it can be split into two parallel core members, electrically isolated from each other, where one serves as the positive lead, while the second, one as the negative lead. 
     At the proximal side of the guidewire the leads (of any type) can either end as bare leads—directly connected to the external electrical current driver, or make use of a connector, preferable a miniature connector, for ease of operation. 
     It should be noted, that the number of the leads may also be greater than two, and depends on the number of the independent coil segments implemented in the distal portion of the guidewire. 
       FIG. 17  shows a schematic configuration of the external current driver, and its derived capabilities. 
     The external driver  160 , generally comprises the following modules: 
     A termination module  172 , used to connect the leads of the guidewire by providing a positive and a negative signals,  174  and  176  accordingly. 
     A signal output generator  162 : The current fed through these terminations to the guidewire is generated by a signal output generator  162 . The figure illustrates a single signal generator, although multiple generators are may also be employed, connected to multiple termination modules. This generator can provide current into the guidewire coils, at different amplitudes, frequencies, and shapes. Preferably the output signal generator will provide sinus, rectangle, and triangle signals, at amplitude of up to 10 amperes, and frequencies at the range of 5 to 1000 Hz. 
     A signal analyzer comprising of three main submodules: 
     Signal input module  170 . Responsible for sensing the current fed into the coils, while measuring the voltage developing on said coils, at different frequencies. 
     A signal analyzing module  168 . Responsible to analyze the measured signals delivered by the signal input module  170 . Such analysis is done by means of digital signal processing. More specifically the signals delivered from the signal input module  170 , can be used to measure the following parameters: 
     The resistance of the coils. Since the resistance of the coils depends in a known manner on the temperature that surrounds the coil, it is therefore possible to remotely measure and analyze the temperature of the coils, and upon reaching a predetermined temperature limit, to automatically control the auto/manual control module  166  to stop output signal delivered by the signal output generator  162 . 
     The impedance of the coils vs. the frequency of the signal fed into the coils, hence providing data about the organ that is in proximity of the guidewire tip that may be used for increasing the safety of the drilling feature of the guidewire. More particularly, usage of such continuous measuring of the impedance of the coils can be employed to determine whether the guidewire has dissected into the vessel wall, or may be even performing perforation to the vessel wall. 
     An auto/manual control module  166 . Which receive the analysis from the signal analyzing module  168 , which enables for automatic and/or manual control of the signal output generator  162 . In the manual control mode the operator/physician can control the driver in various ways, such as using a keyboard to enter controlled parameters, leg pedal to start/stop the driver, rotating knob etc. The automatic mode enables some or all of the manual functions to be performed automatically, and hence reduces the work load of the physician. For example, upon analyzing a too high temperature developing on the active coils, the driver automatically stops its operation, until temperature returns to normal/allowed level. 
     It should be mentioned that although only a single signal output is shown in the drawing, multiple outputs may be employed enabling the simultaneous and independent driving of several coil leads. 
     All of the above mentioned parameters are given by way of example only, and may be changed in accordance with the different requirements of the various embodiments of the present invention. Thus, the abovementioned parameters should not be construed as limiting the scope of the present invention in any way. In addition, it is to be appreciated that the different tubes, wires, magnets, and other members, described hereinabove may be constructed in different shapes (e.g. having oval, square etc. form in plan view) and sizes differing from those exemplified in the preceding description. 
     The above examples and description have been provided only for the purpose of illustration, and are not intended to limit the invention in any way. As will be appreciated by the skilled person, the invention can be carried out in a great variety of ways, employing more than one technique from those described above, all without exceeding the scope of the invention.