A therapeutic endo-rectal probe and apparatus constituting an application thereof for destroying cancer tissue, in particular of the prostate, in combination with an imaging endo-cavitary-probe

Abstract: A therapeutic endo-rectal probe comprises at least a piezoelectric transducer element mounted in a support member itself connected to a rigid guide means enabling endo-rectal insertion of said probe, the outside shape of said support member preferably being that of a disk having an outline that is for the most part substantially circular or substantially elliptical, thereby facilitating endo-rectal insertion.

Description: The present invention relates essentially to a therapeutic endo-rectal probe, and also to apparatus constituting an application thereof for destroying tumor tissue of the prostate in combination with an imaging endo-cavitary probe. Tumor tissue, in particular of the prostate, is preferably destroyed by the action of ultrasonic soundwaves that are pulsed and focused. BACKGROUND OF THE INVENTION It is already known that tissue can be destroyed by being subjected to a given "heat dose". At a given temperature, the heat dose is a function of the length of time that heat is applied. Various means have been proposed for raising temperature, in particular by using infrared radiation or microwave radiation, (see Biodan's US patent 4 823 812, inventor Eshel). When using these methods, it is not possible to cause selective heating of the tissue insofar as the radiation is omnidirectional and cannot be focused on a target zone. In addition, these methods are not adapted or are poorly adapted to treating zones of deep tissue. (See the article by Fry entitled "Threshold ultrasonic dosage for structural changes in mammalian brain" published in JASA (1970, 48 , 1413-1417)). To solve this problem, in IEEE Transactions on sonics and ultrasonics, Vol. SE-31, No. 5, September 1984, pp. 473-480, Lizzi et al. propose using soundwaves that are focused to obtain tissue-destroying hyperthermia. As a result, soundwaves of sufficient energy when applied for a sufficiently long period of time serve to reach a "heat dose" threshold required for destroying the target tissue. The Document WO 89/07909 also describes an apparatus for locating and destroying tumors by ultrasonic hyperthermia, the apparatus comprising the features of the preamble of claim 1. An apparatus is also known from Document EP-A-0 363 239 for localized destruction of soft structures by means of focused negative elastic pressure waves suitable for giving rise to a cavitation phenomenon in the tissue subjected to the sound. The cavitation phenomenon has the effect of giving rise to localized large mechanical stresses at the cavitation location, thereby destroying the tissue concerned. When using soundwaves, tissue is generally destroyed by a combination of the cavitation effect and of the heating effect. Unfortunately, the three-dimensional position of where cavitation takes place is difficult to control because cavitation takes place preferentially at the various interfaces encountered by the soundwaves, such as those associated with the skin, with various organs, or with blood vessels. For example, when applying treatment from outside the body as described in EP-A-0 363 239, there is a danger of cavitation phenomena arising anywhere along the path followed by the wave propagating between the transducer and the zone of focus. Given that such cavitation phenomena are destructive, it becomes difficult to control the therapy and to limit it to the target zone. In addition, the presence of cavitation bubbles on the path of the soundwaves gives rise to a sound screen such that the treatment loses some of its efficiency. It can thus be seen that it is highly advantageous to minimize the path followed by the sound to reach the focus zone, thus reducing the number of interfaces to be passed through. In other words the transducer is advantageously placed as close as possible to the zone of treatment. Such closeness also has the advantage of improving the accuracy with which the therapy is applied. This approach has already been described in Document WO-A-89/07909, Figure 5, where a rectal probe has been developed for treating tumors of the prostate. The device described is based on using two transducers incorporated in the rectal probe. One serves as a device for observing and locating the prostate, and the other serves to emit waves of ultrasound to perform the therapy. The therapeutic transducer is coupled to a mirror for reflecting soundwaves. By coupling rotation of the mirror to displacement of the transducer relative to the mirror, it is possible to scan and treat a sector of the prostate. By rotating the assembly, it is possible to treat a given volume of the prostate. The transducer component must be capable of moving very considerably relative to one another in order to make it possible to treat the entire volume of the prostate. This gives rise to a mechanical device that is complex to the detriment of the ease with which it can be used and above all of its accuracy, as is required for this type of therapy. In addition, that device cannot be used simultaneously to locate and to treat the tumor zone. Each time a zone is located, it is necessary to displace the observation device to leave room for the treatment device. A major drawback of this is loss in the accuracy with which treatment is applied, with such loss being due in part to tissue moving when the transducer components are moved. Another major drawback of that device is that progress of the treatment cannot be monitored in real time and the position of the probe cannot be corrected in real time as a function of the results obtained. An object of the present invention is thus to solve the novel technical problem consisting in providing a solution for destroying tumor tissue (in particular of the prostate), the apparatus being simple to use, accurate, reliable, and capable of simultaneous monitoring in real time. Another object of the invention is to solve the novel technical problem consisting in providing a solution for destroying tumor tissue (in particular of the prostate) by means of a solution that is sufficiently simple, accurate, and reliable for it to be possible to consider treating tumors (in particular of the prostate) at an early stage, i.e. when the lesions are small in size and thus require observation means and treatment means that are extremely accurate. Another object of the present invention is to solve the novel technical problem specified above by approaching the tumor tissue via the rectum. An object of the present invention is to solve the novel technical problem specified above by approaching the tumor tissue (in particular of the prostate) via the rectum, while simultaneously observing the tumor tissue in real time via endo-cavitary means. Another object of the present invention is to solve the novel technical problems specified above by adopting a solution that makes it possible to approach the tumor tissue simultaneously via the rectum for the therapeutic device and via endo-cavitary means for the real time observation device. Another object is to solve the novel technical problems specified above by a solution that uses focused ultrasonic soundwaves of short duration and high intensity. In the description and the claims, the term "short duration" is used for periods of exposure to sound that are less than sixty seconds long, in contrast with conventional hyperthermia. All of these technical problems are solved by the present invention simultaneously, simply, safety, and reliably in a manner that is susceptible of industrial application. SUMMARY OF THE INVENTION Thus, the present invention provides a therapeutic endo-rectal probe as defined in claim 1 Embodiments thereof are defined by the claims dependent thereon. BRIEF DESCRIPTION OF THE DRAWINGS Embodiments of the invention are described by way of example with reference to the accompanying drawings, in which: Figure 1 is a diagrammatic profile view in partial section showing the therapeutic endo-rectal probe in position in the rectum together with an endo-cavitary probe here under the form of an endo-urethral probe in position in the urethra and level with the prostate; This embodiment is not claimed. Figure 2 is an axial view in longitudinal section on line II-II of Figure 3 through the endo-rectal probe together with the rigid guide means supporting it; Figure 3 is a view looking along arrow III of Figure 2; Figure 4 is a section view on line IV-IV of Figure 3 through a first embodiment of a transducer element as shown in Figures 2 and 3; Figure 5 is a plan view similar to Figure 3 showing a second embodiment of an endo-rectal probe of the present invention having a smaller diameter in the direction perpendicular to the direction of longitudinal endorectal insertion; Figure 6 is a section on line VI-VI of Figure 5; Figure 7 is a plan view of a third embodiment of a transducer element which is elliptical in shape; Figure 8 is a section view through the elliptical transducer element of Figure 7 on line VIII-VIII of Figure 7; Figure 9 shows a variant embodiment of the endo-rectal probe shown in Figures 1 to 4, including an axially-deformable inflatable membrane shown in the inflated state; including an optional version embodiment with a thermocouple inside the catheter and another optional version embodiment with a pressure sensor; Figure 10 is a block diagram of control members for the apparatus. Figure 11 shows another embodiment of a therapeutic endorectal probe of the present invention diagrammatically and in fragmentary section, this endorectal probe further including an imaging endo-cavitary probe comprising an imaging transducer, said imaging endo-cavitary probe constituting an imaging endo-rectal probe, with the present view being similar to that of Figures 4 and 9; Figure 12 is a plan view of the endorectal probe of Figure 11; Figure 13 shows another embodiment of an endorectal probe of the invention fitted with an imaging endo-cavitary probe here comprising a commercially available endo-rectal imaging transducer by means of a fixing clamp; Figure 14 is a longitudinal axial section view through the fixing clamp as seen on arrow XIV of Figure 13. Figure 15 shows a further embodiment of an endo-rectal probe of the invention of a structure allowing insertion of an imaging endo-cavitary probe, here comprising a commercially available endo-rectal imaging transducer, under the therapy transducer which comprises an acoustical window through which said imaging transducer performs a sector scanning permanently covering the focal point and the treatment zone; Figure 16 is a plan top view of the endo-rectal probe of figure 15. DETAILED DESCRIPTION The embodiment of fig. 1 is not according to the invention but helps in understanding the disclosure. Fig.10 as much as it refers to fig.1 is also not according to the invention. With reference to the figures, and in particular to Figures 1 to 3, there can be seen apparatus for destroying tumor tissue 2, in particular of the prostate 4, with the apparatus being given overall reference numeral 10. The bladder is referenced 16, the patient is referenced 6, and the urethra 8. The apparatus comprises an endo-rectal probe 12 inserted in the rectum R, together with an endo-urethral probe 14 for observation purposes and inserted in the urethra 8. According to the invention the therapeutic endo-rectal probe 12 comprises at least one piezoelectric transducer element 20 having a front face 20a for emitting ultrasonic soundwaves and a rear face 20b. The transducer element 20 is mounted in a support member 30 which is itself connected to rigid guide means 32 enabling endo-rectal insertion of the probe to be performed, as can clearly be seen from the figures. The outside shape of the support member 30 is preferably in the form of a disk having an outline that is substantially circular (see Figure 3) or that is substantially circular over a major portion (see Figure 5), or that is substantially elliptical (see Figure 7), thereby facilitating endo-rectal insertion. In a particular variant embodiment, the support member 30 is substantially closed, but includes a front face 30a provided with an opening 34 which can be seen more clearly in Figure 2, leaving the front face 20a of the transducer element 20 substantially completely uncovered, so as to avoid interfering with the emission of ultrasonic waves. The outside perimeter of the support member 30 is advantageously defined in such a manner that in a radial plane perpendicular to the longest longitudinal axis, it is never greater than about 16 cm. Advantageously, the support member 30 is made up of two por tions: a front portion 35; and a rear portion 36, which por tions can be taken apart to provide easy access to the trans ducer element 20. It may be observed that the front portion 35 is provided in this case with at least two radially projecting annular shoulders given respective references 37 and 38 for constituting reception surfaces respectively for the periphery of the transducer element 20 and for the rear portion 36. It is advantageous to leave clearance between the trans ducer element 20 and the rear portion 36 of the support member 30 in order to leave room to receive an intermediate or backing layer having the function of improving the performance of the transducer element 20. The nature of such intermediate layers or backing is well known to the person skilled in the art. The rear portion 36 is disconnectably fixed to the front portion 35 in any suitable manner, e.g. by means of fixing screws (not shown) but symbolized by axes 39. Sealing means 40 may be provided between the front and rear faces 20a and 20b of the transducer element. The sealing means 40 advantageously comprise a resin that is preferably electrically conductive. In addition, an electrically insulating gasket 42 may be provided (an annular gasket in this case) to insulate the rear face 20b of the transducer element 20 electrically. The above-mentioned support guide 32 advantageously comprises a rigid tube that is seen more clearly in Figure 2, having a distal end 32a on which the support element 30 for the transducer element is mounted and a proximal end 32b enabling at least one electrical wire 44 to pass along the tube to power the transducer element 20. It is preferable for the support member and the rigid guide 32 to be made of an electrically conductive material such as a metal, and in particular brass, and for it to be grounded as shown symbolically in Figure 2. As a result, the electrical feed wire 44 serves merely to apply positive current to the transducer element 20 in a manner well known to the person skilled in the art. In an advantageous embodiment of the invention, the endo-rectal probe 12 includes a membrane 50 which can clearly be seen in Figure 7, which membrane completely surrounds the piezoelectric transducer element 20, being mounted on the support member 30 or on the guide means 32. In the example shown it is mounted on the guide means 32 by means of a sleeve 62 enabling the guide 32 to move in rotation and in translation in a fully sealed manner, with means being provided to feed a liquid coupling medium 52 to the inside of the membrane 50. These feed means preferably comprise a feed pipe 54 disposed inside the hollow rigid tube 32, with the pipe engaging in a corresponding orifice formed through the solid support member 30, thereby putting the feed pipe 54 into communication with the space defined between the membrane 50, the sleeve 62, and the support member 30. The membrane 50 is advantageously constituted by a material that is thin and flexible, and that is transparent to soundwaves, e.g. a latex or a silicone. The sleeve 62 includes an annular groove 64 receiving the end or mouth 52 of the membrane 50 which is formed in this case into a pocket or bag, and also receiving means 66 such as a clamping collar for fixing the membrane 50 in place. In another advantageous embodiment of the invention, the above-mentioned membrane 50 includes radial deformation means 56 for enhancing radial deformation of the membrane significantly without deforming it longitudinally, thereby enabling the membrane 50 to come into contact (at 50a) with a patient's rectal wall 60 without expanding significantly along the longitudinal axis defined by the axis of the guide means, and also referred to as the X-axis in Figure 1. The above-mentioned radial deformation means 56 preferably comprise a zone 50a of reduced thickness in the membrane overlying the above-mentioned transducer element, thereby ensuring contact with the rectum wall 60 over the entire area of the transducer element 20 and even over a greater longitudinal distance so that when the coupling liquid 52 is injected by suitable coupling of the injection means (not shown), good contact is provided with the rectal wall 60. The longitudinal size of the membrane 50 is preferably longer than that of the support member 30 so as to enable the support member 30 to move relative to the membrane 50, in particular in longitudinal translation, with the support member 30 moving inside the membrane 50 as will readily be understood on observing Figure 9. In another optional advantageous embodiment shown on Figure 9, the above-mentioned membrane 50 includes a catheter 500 fixed on its outside face. This catheter allows the insertion of a thermocouple 510 which can be placed in contact with the rectal wall. The position of the thermocouple 510 is approximatively on the center of the zone 50a of reduced thickness shown on Figure 9. This thermocouple 510 permits the control of the temperature of the rectal wall during the treatment. According to another optional advantageous feature of the invention, shown in Figure 9, the support member 30 comprises a pressure sensor 520 in order to control acoustic pressure field generated by the transducer and to check that the membrane 50 is correctly inflated. This pressure sensor 520 is placed on the top face of the support member in the coupling liquid volume closed by the membrane 50. It gives two different informations: the acoustic pressure level to control the therapeutical ultransonic pressure field and the static pressure inside the membrane 50. This last information is of great importance to be sure that the coupling between the transducer element 20 and the rectal wall is correct. The electrical connections 530 of the pressure sensor 520 follow the same path as the electrical connections of the transducer element 20. According to another optional advantageous feature of the invention shown on Figure 9, the support member includes an endoscopic supervision device. This device comprises at least one optical fiber 540 inserted inside the support member 30 and the rigid tube 32. The fiber tip terminates on the top face of the support member 30 to allow the vision of the rectal wall through the membrane. The opposite fiber tip could be either connected to an optical lens or an a CCD camera in order to follow the treatment process in a very simple and safe way. Advantageously, the transducer element 20 focuses the ultrasonic waves on a focal point and is preferably selected from the group constituted by conventional piezoelectric ceramics and by composite piezoelectric ceramics. The transducer element may be of monolithic design, being plane in shape and coupled to a focusing lens that is of monolithic design and in the form of a spherical cap that naturally focuses soundwaves emitted at the geometrical center of the sphere. Alternatively, the transducer element 20 may be of a mozaic design with focusing being obtained by electronic means associated with each of the elements in the mozaic, or the mozaic may be in the form of a spherical cap, with focusing being obtained naturally. In Figures 1 to 9, it will be seen that all of the embodiments show a presently preferred form where the transducer element is in the form of a spherical cap of the type having natural focusing. In a preferred embodiment of the invention, the above- mentioned transducer element has a ratio of the diameter (d) of its ultrasound wave emitting front face 20a divided by its focal length (F) which may be natural or obtained by electronic means, that lies in the range above 0.5 to about 1.5, that lies preferably in the range about 0.8 to about 1.2, and better still is about 1. With reference to Figures 1 to 4, a monolithic transducer element is shown that is in the form of a spherical cap of circular section having its diameter symbolized by d , its focus F, its focal length by f , and its bulk or apparent thickness e . With reference to Figures 5 and 6, another embodiment of an endorectal probe is shown in which parts that perform the same function have been given the same reference numerals plus 100. It may be observed that the major portion of the outside shape of the transducer element 120 is substantially circular, with the same applying to the support member 130, but that the dimension (d'1) in a direction perpendicular to the axis of the rigid guide 132 is smaller than the diameter (d1) parallel to the axis of the rigid guide 132, as is clearly visible in Figure 5. This smaller diameter d'1 may be obtained by cutting off the sides 121 and 122 of the transducer element 120, and similarly by cutting off the sides 131 and 132 of the support member 130, with the resulting shape facilitating endo-rectal insertion. As a result, the diameter of the transducer element 120 and also of the support member 130 varies instead of being constant. Advantageously, the ratio of the diameter in the longitudinal direction (d1) divided by the diameter in the direction perpendicular to the longitudinal axis (d'1) lies in the range 1 to 2. In accordance with another advantageous characteristic of the invention which is applicable to all embodiments, the outside perimeter P, P1 or P2 of the support member 30, 130 in the radial plane perpendicular to the longer longitudinal axis always remains below about 16 cm, thereby making endo-rectal insertion possible. Figures 7 and 8 show another embodiment of a transducer element, with the reference numerals being increased by a further 100. Thus, the transducer element is referenced 220. In this case, it is essentially elliptical in shape having a long diameter d2 extending parallel to the longitudinal axis of the patient 6, in this case the X-axis of Figure 1. The shorter diameter is d'2 and its perimeter is P2, with its apparent thickness being e2, and its focal length being f2. The focal length f , or f1 or f2 of the transducer element advantageously lies in the range 2 cm to 7 cm, and is ideally about 5 cm, depending on the penetration depth desired for the soundwaves. The diameter d or d' has a value lying in the range 2 cm to 7 cm, and is ideally about 5 cm, depending on the energy density level that is acceptable at the transducer element 20. The particular geometrical shapes shown in Figures 5 to 8 has the advantage of increasing the emission area of the transducer without increasing its diameter, or of retaining the same emission area while reducing the area of the transducer. In addition, the above-mentioned rigid guide 32 may be 20 cm long and may have a diameter of about 12 mm. In addition to having the function of containing the coupling liquid 52, the membrane 50 also provides a sterile barrier at the end of the rectal-probe 12. The membrane is itself sterile and is designed to be easily interchangeable, e.g. for use on a single occasion only. The above-mentioned apparatus includes an imaging endo-cavitary probe 14 shown in Figure I in the form of an endo-urethral probe working in combination with the above-described endo-rectal probe. Note that in Figures 11 to 16, the imaging endo-cavitary probe is shown in the form of an imaging endo-rectal probe, comprising a commercially available endo-rectal imaging transducer. Advantageously, the imaging endo-cavitary probe is of the ultrasonic type having image-forming means (not shown) for forming an image by echography. According to another particular characteristic of the invention, the endo-cavitary probe 14 includes a transducer element 70 as can clearly be seen in Figure 1, which probe is mounted on a support element 72 which is itself mounted on rigid guide means 74 for the endo-cavitary probe. In reference to Figure 1, the endo-rectal probe 12 and the endo-urethral probe 14 are preferably mounted via their respective guide means 32 and 74 on a common support device 80 for both probes 12 and 14, the support device preferably including a rigid column 80 mounted on a device 82 for supporting the patient. Encoding devices 98 and 100 are also shown integrated in the couplings 84 and 86 (not shown explicitly in Figure 10, but known to the person skilled in the art) and these encoding devices co-operate with the motor and gear box devices 94 and 96 to measure accurately the displacement in translation and/or in rotation of each of the probes 12 and 14 as represented diagrammatically in Figure 10. Means 92 are also provided for transmitting this information concerning displacement in translation and/or rotation to the control device 90. The control device 90 may include a central computer, in particular a computer containing control software, which software is preferably constituted by operator interface software and command management software. The control interface is advantageously a portion of the transmission means 92 shown in Figure 10. Via the interfaces 92, the command management software controls the motors 94 and 96 integrated in the couplings 84 and 86 for moving the endo-rectal and endo-urethral probes and receives information concerning the displacement of the probes as transmitted by the encoders 98 and 100 integrated in the couplings 84 and 86. The observation transducer element of the endo-urethral probe 14 is preferably of the ultrasonic type and thus constitutes an echograph. It provides an image plane of the urethral wall 8, of the prostate 4, and of the rectal wall 60 as can clearly be seen in Figure 1. The support guide element 74 ensures that the transducer element 70 is rigidly positioned inside the urethra 8. The endo-rectal and endo-urethral probes can be moved in translation and in rotation either manually or else using the above-mentioned motor devices 92 and 94 integrated in the couplings 84 and 86 and under the control of the control device 90. With reference to the figures, the apparatus operates as follows: Initially the endo-urethral probe 14 is inserted into the urethra and is placed level with the prostate, in the position shown in Figure 1. The endo-rectal probe 12 is then inserted into the rectum and is placed facing the prostate as shown in Figure 1. The membrane 50 is then filled with coupling liquid which is injected via the inside of the guide tube 32 so that the thin zone 50a of the membrane deforms radially and comes into contact with the rectal wall 60. The two probes 12 and 14 are then fixed relative to the common support 80 via the couplings 84 and 86. The positions of the couplings 84 and 86 are adjusted so as to cause the relative position of the two probes 12 and 14 so as to make the image plane of the endo-urethral probe 14 correspond with the midplane of the endo-rectal probe 12, thereby making it possi ble to keep the focus of the soundwaves from the probe 12 under permanent observation, as can clearly be seen in Figure 1. Thereafter, by displacing the probes 12 and 14 simultane ously in translation along the X-axis direction by means of the couplings 84 and 86, it is possible to retain this relative position and monitor the therapeutic process in real time. Once they are properly positioned relative to each other, the relative position of the two probes is "frozen", thereby ensuring that real time monitoring can be continued throughout the therapeutic process. The observation endo-urethral probe 14 provides a radial image plane through the prostate, thus making it possible to determine the Z and Y coordinates of the volume of tumor to be destroyed. By displacing the endo-rectal and endo-urethral probes 12 and 14 simultaneously along the X-axis, it is possible to keep the prostate under permanent observation along the X-axis, thereby determining the X coordinates of the tumor volume to be destroyed. The X, Y, and Z coordinates of the tumor volume to be destroyed are then recorded by the central computer 90. Thereafter, the central computer 90 controls the motors 94 and 96 for displacing the probes 12 and 14 so as to scan and treat the entire tumor volume. By moving the therapeutic probe 12 along the Z-axis and by rotating it about the X-axis, it is possible to treat the prostate in a radial plane corresponding to the image plane of the probe 14. By displacing both probes 12 and 14 simultaneously along the X-axis it is also possible to treat successive planes, thereby treating the entire volume of the tumor to be destroyed while retaining the ability to monitor the therapeutic process in real time. A method of destroying tumor volumes, in particular in the prostate, is also diclosed the method comprising: providing an endo-rectal therapeutic probe capable of emitting focused ultrasonic soundwaves; providing an imaging endo-cavitary probe; providing control means for controlling displacement of said probes in translation along an axis parallel to the longitudinal axis of the patient, and control means for controlling rotation of said probes about said axis, referred to as the "X-axis"; inserting the endo-rectal probe into the rectum to bring it level with the tumor volumes to be treated, in particular the prostate; inserting the imaging endo-cavitary probe in regard to said tumor volumes to be treated, so that the image plane of the endo-cavitary probe corresponds to the midplane of the endo-rectal probe, thereby observing the focus of the soundwaves emitted from the endo-rectal probe; and When so desired, displacing in translation simultaneously the endorectal probe and the endo-cavitary probe, thereby treating the entire volume of the tumor to be destroyed while permanently observing the focus of the endorectal probe. This method comprises the steps of: providing an endo-rectal therapeutic probe capable of emitting focused ultrasonic soundwaves; providing an imaging endo-cavitary probe; providing control means for controlling displacement of said probes in translation along an axis parallel to the longitudinal axis of the patient, and control means for controlling rotation of said probes about said axis, referred to as the "X-axis"; control means for controlling displacement of said probes in translation along an axis perpendicular to said X-axis, thereby enabling the said probes to be moved towards each other or away from each other along an axis referred to as the "Z-axis"; inserting the endo-urethral probe into the urethra to bring it level with the tumor volumes to be treated, in particular the prostate; inserting the endo-rectal probe into the rectum to bring it level with the tumor volumes to be treated, in particular the prostate; fixing both the endo-urethral probe and the endo-rectal probe to a common probe support device so that the image plane of the endo-urethral probe corresponds to the midplane of the endo-rectal probe, thereby observing the focus of the soundwaves emitted from the endo-rectal probe; and simultaneously displacing both the endo-urethral probe and the endorectal probe along the X-axis during the therapeutic process so as to cover the volume of the tumor to be destroyed. When so desired, the endo-rectal probe is also displaced in translation along the Z-axis while rotating the endo-rectal probe about the X-axis, thereby treating the entire volume of the tumor to be destroyed. According to the invention the endo-cavitary probe is physically linked to the endo-rectal probe, thereby facilitating insertion of the two probes in a single step and also avoiding the step of putting in proper position the imaging endo-cavitary probe with regard to the endo-rectal probe. In an advantageous variant implementation the endo-rectal probe includes a transducer element that is focused naturally or electronically, and in which the ratio of its diameter to its focal length lies in the range 0.5 to 1.5, and preferably in the range 0.8 to 1.5, and better still is about 1. In another advantageous implementation, the transducer element 20 is caused to admit ultrasound waves pulsed at a frequency lying in the range 1 MHz to 4 MHz with pulses that are of short duration, lying in the range 50 ms to 5 s, and preferably in the range 200 ms to 2 s, with the intensity at the focus lying in the range 1,000 W/cm 2 to 10,000 W/cm 2 . It should also be observed that the longitudinal length of the above-mentioned membrane is sufficient to enable the support member to move in axial translation, and in particular its radial deformation means extend longitudinally over a distance greater than the longitudinal length of the support member so as to enable displacement movement of the support member, in particular in translation, inside the membrane without losing contact between the membrane and the rectal wall. In yet another advantageous embodiment as shown in Figures 11 and 12, the therapeutic endorectal probe 12 is of the same type as that described with reference to Figures 1 to 4 and further includes an imaging endo-cavitary probe comprising an imaging transducer designated by overall reference numeral 300. This imaging endo-cavitary probe is secured to the therapy transducer 20 via the endo-rectal probe 12, thereby constituting an imaging endo-rectal probe of a fixed position relative to the endo-rectal probe 12. The imaging transducer 300 is advantageously separate, being independent from the therapy transducer and pointing so that its image plane as symbolized by the letters PI continuously includes the axis of symmetry shown in Figure 11 of the therapy transducer 20 and the focal point F, thereby enabling the focal point and the treatment zone to be continuously displayed. In a particular variant embodiment, the imaging probe 300 performs by sector scanning, as shown. In the example shown in Figures 11 and 12, the imaging transducer element 300 is secured to the support 32 of the endorectal probe 12, e.g. by gluing. In another embodiment shown in Figures 13 and 14, the endorectal probe 12 also includes an endo-cavitary probe 400 comprising a commercially available endo-rectal imaging transducer which is secured to the support 32 of the endorectal probe 12 and thus to the therapy transducer 20 by means of a fixing clamp 402 which is shown in greater detail in Figure 14. The fixing clamp 402 advantageously includes guide means formed in this case by two longitudinal channels 404 and 406, and it extends over a sufficient length longitudinally in order to be able to perform this guidance function. In addition, sealing means such as O-rings are advantageously provided such as 408 & 410, and 412 & 414. These scaling means are advantageous insofar as it is possible to provide a membrane 50 filled with liquid and surrounding the therapy and imaging transducer elements 12 and 400 as in the preceding embodiments. The advantage of this embodiment shown in Figures 13 and 14 lies in the fact that it is possible to use commercially available imaging probes which are merely inserted in the guide channel 404 until they take up the precise position shown in Figure 13 which forms an integral part of the invention. In this position, the imaging transducer 400 is set back from the therapy transducer 20, thus ensuring that it does not interfere with it in any way while nevertheless having its image plane PI pointed to occupy the axis of symmetry of the therapy transducer 12 on a permanent basis, including the focal point F, thereby making it possible as in the preceding embodiment, to display the focal point and the treatment zone on a permanent basis. In a further embodiment shown in Figures 15 and 16, which represents a variant of the embodiments shown in Figures 13 and 14, the same reference numbers have been used for identical parts. Here it will be clearly understood for one skilled in the art that the imaging endo-cavitary probe 400 is inserted in a blind opening 450 which extends at least in part under the therapy transducer 20. The therapy transducer 20 comprises an acoustical window 460 under which is positioned the acoustic source 462 of the imaging probe 400 thereby allowing image scanning through the acoustic window 460 according to an image plane permanently covering the focal point and the treatment zone. Here it can be shown from figure 16 that the image plane is substantially perpendicular to the symmetry axis of the endo-rectal probe since it represents the scanning plane which is obtained with the commercially available endorectal probes. In a preferred embodiment, the imaging transducer 300 or 400 operates at a frequency lying in the range 3 MHz to 7 MHz.

Claims: A therapeutic endo-rectal probe (12) for treating human beings by emitting focused ultrasound waves, comprising at least a piezoelectric therapy transducer element (20) having a front face (20a) for emitting ultrasonic soundwaves focused on a focal point and a rear face (20b) and an imaging transducer (300, 462) said therapy transducer element (20) being mounted in a support member (35, 36) itself connected to a rigid guide means (32) enabling endorectal insertion of the probe, characterised in that the imaging transducer (300, 462) is fixed with respect to the therapy transducer element (20), so that the focal point of the therapy transducer element (20) is comprised in the imaging plane of the imaging transducer, and in that the imaging transducer (300, 462) is secured to the therapy transducer element (20) or to a support (32) of the therapy transducer element (20). The probe of claim 1, wherein the therapy transducer element has a shape that naturally focuses ultrasonic soundwaves. The probe of claim 1, wherein the therapy transducer element is electronically focused. The probe of claim 1, 2 or 3, wherein the imaging plane contains the axis of symmetry of said probe. The probe of claim 1, 2 or 3, wherein the imaging plane is substantially perpendicular to the axis of symmetry of said probe. The probe of one of claims 1 to 5, wherein the therapy transducer element (20) comprises an acoustical window (460). The probe of claim 6, wherein the imaging transducer (400) is located under the acoustical window (460). The probe of one of claims 1 to 5, wherein the imaging transducer (300) is glued to the support. The probe of one of claims 1 to 5, wherein the imaging transducer (300) is secured to the support by a fixing clamp (402). The probe of one of claims 1 to 9, wherein the imaging transducer (300, 400) performs by sector scanning. The probe of one of claims 1 to 10, wherein the imaging transducer operates at a frequency lying in a range from 3 MHz to 7 MHz.

Inventors: BLANC EMMANUEL, CATHIGNOL DOMINIQUE, CHAPELON JEAN-YVES, GELET ALBERT, BLANC, EMMANUEL, CATHIGNOL, DOMINIQUE, CHAPELON, JEAN-YVES, GELET, ALBERT
Applicants: INST NAT SANTE RECH MED, TECHNOMED MEDICAL SYSTEMS, INSTITUT NATIONAL DE LA SANTE ET DE LA RECHERCHE MEDICALE (INSERM)
Application year: 1992
Main classification: A61B17
IPC codes: A61N7, A61B17