the process according to the present invention is particularly remarkable in that cleaning and enlargement of canals , or other passages , particularly those formed by mineral and organic substances , can be effected by provoking a cavitation of vapor within a liquid present or introduced in the passage by the delivery of energy , in the form of laser radiation , to the interior of the canal , and focussing the radiation , with the aid of an optical fiber . in an advantageous manner , according to the application of the invention to the cleaning and enlargement of tooth canals , the irrigating fluid is water , which may be demineralized or mineralized , and in a particularly advantageous manner , a type of irrigation solution most frequently employed during the performance of dental procedures in a canal , i . e ., water containing 0 . 5 - 2 . 5 % naclo . the radiation absorption minimum of this liquid corresponds to a wavelength of between 0 . 530 and 1 . 06 μ . this wavelength corresponds to the characteristic wavelengths of nd - vag lasers , whose radiation wavelength can be regulated to have a value of 0 . 530 , 0 . 750 , or 1 . 06 μ . use can also be made of ruby lasers whose wavelength is 0 . 694 μ . to obtain a cavitation of vapor in this liquid , the liquid being transparent to these wavelengths , it is sufficient to focus the laser radiation to create a point at which there is a high light intensity . in an advantageous manner , this cavitation of vapor is created by means of a beam or radiation from a yag laser which permits the energy to be transported with the aid of an optical fiber that is sufficiently thin to be introduced into a tooth canal ( 0 . 30 mm ) in a manner to focus , or concentrate , the radiation at the free end of the fiber . the free end of the fiber can be given the form of a lens having a focal length selected to permit displacement of the zone of cavitation by a desired distance from the free end of the fiber , which assures the creation of an enlargement action at various distances from the free end of the fiber . thus , the focal length imparted to this lens at the free end of the fiber permits a focussing of the radiation at a location more or less spaced from the free end of the fiber . focussing of the laser beam creates , at the focal point , the generation of a bubble which then implodes while provoking an erosion of the adjacent canal wall . fig1 and 2 illustrate a tooth 2 having a dental or radical canal 1 . after canal 1 is opened via the crown of tooth 2 , an optical fiber 3 having its free end shaped in the form of a converging lens 4 , 4 &# 39 ; is introduced into canal 1 . lens 4 of the embodiment shown in fig1 has a shorter focal length than does lens 4 &# 39 ; of the embodiment shown in fig2 . laser radiation in the form of pulses conducted via fiber 3 is focussed to create a zone of cavitation 6 . focussing of the radiation beam creates , at the focal point of lens 4 or 4 &# 39 ;, a bubble which , upon termination of the laser radiation pulse , implodes while provoking an erosion of the adjacent wall of canal 1 . depending on the focal length of lens 4 or 4 &# 39 ;, the cavitation will be provoked at a greater or lesser distance from lens 4 or 4 &# 39 ;. cleaning of canal 1 is achieved by shock waves resulting from the laser radiation pulses , producing vapor implosions which detach debris or tissue from the wall of canal 1 . the size of the cavitation bubbles decreases as the focal length increases , a preferred focal length being between 1 and 10 mm . the length , or duration of each laser radiation pulse will be selected in dependence on the diameters of fiber 3 and canal 1 and vary over a wide range . for certain applications , it has been found that a pulse duration of 10 - 20 ns is suitable . however , longer pulse lengths can be employed , particularly for larger fiber and / or canal diameters . the energy of each radiation pulse is also selected on the basis of fiber and canal diameters . while the energy per pulse can be of the order of 0 . 5 to 5 mj , higher energy levels can be employed , particularly for larger fiber and / or canal diameters . a shock wave produced by each radiation pulse propagates and terminates within a period of 50 nanoseconds and a pulse repetition rate of between 1 and 100 hz can be suitably employed . there will now be described an example of the practice of the present invention , which example is not intended to be limitative of the scope of the invention . during a first period , an access passage is prepared , i . e ., the tooth canal or radical canal 1 is enlarged to a diameter of 0 . 25 mm by means of conventional instruments , such as files , along the entire length of the root canal of tooth 2 , to a point about 1 mm from the apex . penetration by the files may be monitored by radiologic means . this corresponds to the first step of an endodontic procedure which is here carried out in a conventional manner . then , irrigating liquid 5 is introduced into canal 1 , for example with the aid of a syringe , and the free end of fiber 3 is introduced into canal 1 , the other end of fiber 3 being coupled to a laser . in addition , liquid 5 can be introduced around fiber 3 during and after insertion of the latter to ensure that canal 1 is filled with the liquid continuously during the cleaning and enlargement , or shaping , process . for a straight canal , an optical fiber having a diameter of 0 . 30 mm with a lens 4 having a short focal length , as shown in fig1 permits widening of the upper third of canal 1 , by utilizing a sequence of laser radiation shots which can have the following parameters : a pulse duration of 10 ns to several milliseconds ; and energy per pulse of 2 mj to 1 j ; and a repetition rate of 30 - 100 hz . this operation is continued until the diameter of canal 1 is increased to 0 . 80 mm . then , use can advantageously be made of a second optical fiber having a diameter of 0 . 30 mm with a lens 4 &# 39 ; having a longer focal length as shown in fig2 to the apical two thirds of the root . the progress of the shaping can be monitored after each sequence of laser radiations shots , or pulses . for the cleaning and shaping of curved tooth canals , the utilization of only an optical fiber having a lens with a short focal length is recommended . it will be noted that optical fiber 3 shown in fig1 tapers towards its outlet end . proper selection of the degree of taper helps to concentrate the laser radiation at the free end of fiber 3 . while the description presented above has been with reference to the treatment of root canals , it should be appreciated that the same technique can be employed in a wide variety of situations to clean and enlarge passages in materials such as ceramics , plastics and metals . the technique according to the further invention can further be usefully applied to the difficult task of removing posts which had previously been implanted in the mouth to support artificial filling to restore a tooth . known techniques for performing this operation are difficult to implement and relatively dangerous because they present the possibility of perforating the tooth root . it has been proposed to loosen such posts by means of ultrasonic vibrations , but to date this has only been partially successful . according to the invention , the free end of an optical fiber is brought into contact with the post near the point where the post enters the root and the associated laser is activated at an energy level of 200 to 300 mj , with a repetition rate of 50 hertz and a pulse duration of 0 . 4 to 1 millisecond , the region surrounding the post having previously been filled with a liquid . due to the vibrations produced by the pulses and the cavitation effects resulting from the interaction of the laser radiation pulses with the liquid , the post becomes loosened and can then be removed without exposing the root structure to any damage . moreover , the technique can also be employed in the medical field for cleaning vessels , such as blood vessels , for example to remove plaque deposits , or atheromas . for such applications , the fiber is introduced to the location to be cleaned and the parameters of the radiation pulses are selected on the basis of the nature of the vessel and its diameter . fig3 illustrates a simple device which can be employed for this purpose , which device essentially includes a hollow catheter 7 , which may be made of plastic , is inserted into a blood vessel so that the distal end of catheter 2 is placed a short distance , possibly 1 to 2 millimeters , from the deposit . optical fibre 3 is disposed within tube 7 and its lens 4 may be located in line with the distal end of catheter 7 or slightly retracted therefrom . fiber 3 may have a diameter of the order of 150 microns . the interior of tube 7 is flooded with a suitable physiologic solution which is supplied so as to exit from the distal end of catheter 7 while under a slight pressure . this creates a favorable environment for the cavitation action . then the laser which is connected to the proximal end of fiber 3 is activated so that laser radiation pulses are introduced into the liquid at a focal point beyond lens 4 . the energy of each laser radiation pulse can be in the range of 5 - 200 mj , the preferred value being higher for larger vessel diameters . here again , a pulse repetition rate of 32 to 100 hertz and a pulse duration of 10 ns to several ms may be employed . during or subsequent to application of a series of such pulses , the region being treated can be subjected to suction in order to remove disintegrated material . this technique offers advantages over previously proposed techniques utilizing laser energy , which techniques require that the distal end of the fiber be in contact with the deposit , since it is proven difficult to place the distal end of the fiber in contact with the deposit while being out of contact with the wall of the blood vessel . the technique according to the present invention eliminates the need for the optical fiber to contact the deposit and avoids heating of the blood vessel wall . since fiber 3 can remain substantially completely within catheter 7 , the fiber itself is prevented from contacting the blood vessel wall . while the description above refers to particular embodiments of the present invention , it will be understood that many modifications may be made without departing from the spirit thereof . the accompanying claims are intended to cover such modifications as would fall within the true scope and spirit of the present invention . the presently disclosed embodiments are therefore to be considered in all respects as illustrative and not restrictive , the scope of the invention being indicated by the appended claims , rather than the foregoing description , and all changes which come within the meaning and range of equivalency of the claims are therefore intended to be embraced therein .
a process for cleaning and / or shaping passages , comprising providing an optical fiber having a diameter sufficiently small to be introduced into the passage and having a free end provided with a radiation focussing element ; introducing the free end of the fiber into the passage so that the focal point defined by the radiation focussing element is located adjacent the region to be cleaned or shaped ; providing a liquid in the passage at the location of the focal point of the radiation focussing element ; and supplying pulses of laser radiation to the fiber so that the radiation exits the fiber via the free end to provoke a cavitation of vapor at the interior of the irrigating liquid .