an embodiment of the apparatus according to the present invention is shown in full in fig2 whereas the disposable first part thereof is shown in fig1 . said disposable first part 5 7 includes a catheter part 3 and a distal part 5 for the application of heat and pressure at the site of treatment , in the present embodiment the uterus cavity . the distal part 5 includes a central body 21 comprising a housing 24 and harbouring a heat - releasing element 22 , both having an elongate configuration . the central body 21 is surrounded by a thin flexible and elastic enclosure or balloon 23 , which is distensible under the influence of a pressure medium supplied to the interior of said enclosure 23 in a manner to be illustrated below . the disposable first part 5 7 is furthermore provided with a proximal part comprising conduit means 9 with a first three - way valve 11 and a first attachment stud 12 . as shown in fig1 and 2 conduit means 9 contains an access pipe 10 for the accomodation accommodation of electrical leads extending up to the heat - releasing element 22 . said leads are suitably connected to a voltage source , such as rechargable rechargeable low - volt batteries . said conduit means 9 additionally includes a side - conduit 16 attached at its end to said first three - way valve 11 and including a second three - way valve 15 and an associated second stud 14 . at the other end side - conduit 16 contains a leak - tight housing 18 having an elastic membrane to which a pressure sensor can be attached from the outside for pressure control purposes . proximal part 9 further includes two injection syringes 13 , 19 for a purpose to be described below . each syringe 13 , 19 is provided with a housing or body 25 and 27 , respectively , and their respective front dispensing ends 29 and 31 , respectively , are leak - tightly connected to studs 12 and 14 , respectively . syringes 13 , 19 are furthermore provided with conventional pistons 33 , 35 , respectively , each piston having its piston bar 37 and 39 , respectively , and actuating plates or discs 41 and 43 , respectively . finally , syringe housings 25 , 27 are each provided with an outer circumferential flange 45 and 47 , respectively . as previously indicated fig2 illustrates the assemble apparatus including the disposable first part 7 and a non - disposable part 51 for repeated use . said non - disposable part 51 includes support or platform 53 onto which the different parts of the auxillary equipment are attached . as seen in fig2 syringe 19 is associated with drive means 55 , whereas syringe 13 is associated with drive means 75 . referring now to fig4 and 5 drive means 55 for syringe 19 include a piston bar actuator 57 slideably mounted on platform 53 in the direction of arrows a ). actuator 57 includes a connecting element 59 with a slot 61 for receiving actuating plate or disc 43 . furthermore , actuator 57 contains a through - hole 63 for a threaded bar 65 having an operating nob 67 at its free end and rotatably but axially fixed at its other end . finally , actuator 57 is provided with a side - opening 69 containing a radially displacable threaded element 71 , the function of which is explained further below . as seen in fig4 syringe 19 is arranged on a bed 56 attached to a plate 59 which in turn through a spacer 68 is attached to platform 53 . bed 56 is provided with a slot 60 for receiving the outer circumferential flange 47 of syringe 19 . fig3 illustrates in more detail drive means 75 associated with syringe 13 . again , syringe 13 is arranged on a bed 73 attached to the upper side of platform 53 and is provided with a slot 74 for receiving the outer circumferential flange 45 of syringe 13 . said drive means 75 are provided with an actuator 77 for piston bar 37 of syringe 13 . actuator 77 is slideably mounted on platform 53 in the direction of arrows b ), and has an upper part 81 provided with a recess or slot 79 for receiving actuating plate or disc 41 of syringe 13 . actuator 77 is furthermore provided with a lower part 83 linked to a rotating excenter disc 87 via an arm 85 . fig6 and 7 disclose an alternative embodiment of the apparatus of the inventions wherein syringes 13 and 19 are replaced by one single syringe capable of performing two functions as will be described in the operation of the apparatus below . this alternative arrangement according to fig6 and 7 has the single syringe 13 arranged axially slideable on a bed 89 and contains as before an outer circumferential flange 45 . drive means 75 correspond closely to those described in connection with fig3 . in this alternative embodiment there is arranged an alternative drive means 55 ′ largely corresponding to drive means 55 illustrated in detail in fig4 and 5 but performing the same function in a different manner . drive means 55 ′ are provided with an - upper part 91 extending above platform 53 and provided with a slot 93 receiving flange 45 of syringe 13 . its lower part 57 corresponds functions - wise to actuator 57 according to fig4 and 5 . actuator 57 with its upper part 91 is slideably arranged in platform 53 in the direction of arrows a ). threaded bar 65 is rotatably arranged but axially fixed in a block 66 attached to platform 53 underneath thereof . the remaining parts of drive means 55 ′ are designed and perform in the same manner as described in relation to drive means 55 of fig4 and 5 . fig7 shows an illustrative cross - section along line a — a in fig6 . fig8 and 9 show two embodiments of the central body 21 including the heat - releasing element 22 and the flexible or elastic enclosure or balloon 23 according to fig1 . fig8 shows a detail a system from enabling effective heat transport and heat transfer from the heat - emitting element 119 to the uterus mucosa ( endometrium ). element 119 contains wires 115 for electrical resistance heating thereof . wires 115 are supplied with electric energy via leads 116 entering through canal 135 . apertures 131 in the proximal part of the tubular central body operate as radially acting inlets for a pressurized liquid medium to a valve housing 132 communicating with an inlet canal 135 , the space between central body 21 and enclosure 23 , as well as with canals 121 arranged about and through the heat - emitting element 119 in the middle part of the central body 21 . apertures 133 arranged in the distal part of the central body 21 act as outlets for the pressurized liquid medium from a second valve housing 139 communicating with canals 121 and the space between the central body 21 and the elastic enclosure 23 , said enclosure being liquid - tight sealed around the proximal part of the central body at 151 and being attached to a nose member 141 of the central body . in valve housing 132 back valves 149 are arranged so as to close apertures or openings 131 at over - pressure in the valve housing 132 and opening at a sub - pressure relative to the liquid pressure in the space between central body 21 and the elastic enclosure 23 . a partition 143 having openings 145 is arranged in valve housing 139 . a disc valve 147 is moveable in an axial direction and arranged so as to close openings 145 at over - pressure in valve housing 139 relative to the liquid pressure in canals 121 in the heat - emitting element of the central body or opening at sub - pressure in valve housing 145 , respectively . fig9 shows in detail a central body 21 containing heat - releasing elements 157 of an inherently self - regulating type , such as ptc - material or ferromagnetic material having a curie point . element 157 also contains canals or passages 121 , and said elements 157 and canals 121 are surrounded by a housing 29 . in other respects the embodiment of fig9 corresponds to that of fig8 but with the difference that the disc valve 147 and the associated partition 143 with apertures 145 are now arranged in the proximal part of central body 21 . between the inlet side of the wires 153 and the partition 143 a chamber 155 is arranged . fig9 shows how the liquid medium is forced to circulate into chamber 145 and further in through the wire package 157 at a pressure shock at the same time as valves 149 close apertures 131 . the procedure for performing hyperthermia in a uterus cavity using the apparatus described above including the function of said apparatus will now be explained more in detail . the disposable first part 7 can be stored in a sterile package separate from the stationary part up to the time of treatment when it is assembled with the stationary part 51 in the manner indicated above . although said disposable first part 7 contains a number of elements performing the necessary functions for the operation of the apparatus according to the invention it is interesting to note that all parts thereof , in order to obtain a disposable assembly , can it be produced in large series at a direct cost not amounting to approximately more than between say 25 and 50 usd . at preparation for treatment the syringe 19 is filled with somewhat more than the quantity of sterile liquid medium required to fill up the system and is then connected to stud 14 . by maintaining the disposable part 7 in a vertical position with syringe 19 in a vertical uppermost position and imparting short movements to piston 35 of syringe 19 the system will be filled with liquid and at the same time air can be removed from the system and collected in syringe 19 . syringes 19 and 13 can easily be freed from air by disconnecting them from the system . syringes 19 and 13 are then connected to their respective studs and piston of syringe 19 is positioned so that the enclosure 23 remains in a collapsed condition . the distal part 3 of the applicator is then inserted through vagina , cervix and into the uterus cavity up to the bottom of the cavity . the length of the central body 21 corresponds approximately to the length of the uterus cavity , i . e . normally 4 to 6 cm . next , syringe 19 is attached with its operating end to drive means 55 by inserting disc 43 into slot 61 . syringe 13 , partially filled with liquid , is attached with its rear operating end to drive means 75 by inserting disc 45 into slot 79 . three - way valves 11 , 15 are set so as to establish communication between syringes 19 and 13 and the interior of enclosure 23 , and piston 35 is pushed forward within syringe 19 to expand the flexible enclosure 23 to conform to the surrounding uterus wall . piston 35 is pushed forward until the desired pressure is reached as recorded by the pressure sensor . as seen in fig4 and 5 drive means 55 can be used for free movement of piston 35 in syringe 19 by retracting threaded element 71 to the position shown in fig4 and 5 . on the other hand , by pushing threaded element 71 into engagement with the threaded bar 65 fine adjustment of the position of piston 35 can be attained by rotating nob 67 , whereby fine adjustment of the pressure in the system can be attained . after the filling procedure drive means 75 are started imparting to the piston 33 of syringe 13 a reciprocating motion . at every positive pressure shock a certain volume of liquid is brought to move forward through the conduits up to the inlet canal 135 of the central body ( fig8 ). this has for an effect that simultaneously a corresponding quantity of pressurized liquid medium is forced through canals 121 in the central body 21 in view of the fact that valves 149 are closed at the same time as valve 147 is opened , and a corresponding quantity of pressurized liquid medium will be pushed out into the space inside the flexible enclosure 23 . at every subsequent backward movement of the piston of syringe 13 a corresponding quantity of liquid medium will be sucked back , valves 149 taking the open position shown in fig8 and valve 147 its closed position . it is appreciated that under the influence of the oscillating pressure shocks and the described valve system a powerful and effective circulation in an internal flow circuit of liquid medium at the pressure given by syringe 19 will be provided through canals 121 of the central body 21 and out into the space within the balloon enclosure and back to the central body without hot liquid passing the inlet canal 135 of the catheter to the other parts of the apparatus . thus , circulation takes place only in the distal part of the apparatus , whereas the inlet canal 135 during circulation only serves as a communication conduit for transmitting in a hydraulic manner the oscillating pressure and liquid movement provided by syringe 13 and for maintaining the desired pressure in the system by means of syringe 19 . in the treatment using the apparatus according to the present invention the pressure used in the system varies from case to case and may also vary during the treatment of one and the same patient , in view of for example variations in blood pressure , contractions of muscular tissue etc . a suitable pressure range lies within the interval between about 120 and about 170 mm hg , and a suitable temperature of the circulating liquid is about 65 ° to 90 ° c . the period of treatment for obtaining the desired result varies within relatively wide limits but satisfactory results are usually obtained with a time of treatment varying from about 20 to about 30 min . in order to obtain satisfactory internal circulation it has been found that a reciprocating frequency for the means for internal circulation lies between about 300 and 1000 strokes per min at a stroke volume of about 0 . 1 to 0 . 5 ml . it is to be noted that these values are to be considered only as suitable guidelines and other values lying outside of the ranges given are fully conceivable . by considering the illustrations of fig1 and 2 it is appreciated that fig2 shows the disposable first part 7 which , after use , can be disconnected from the non - disposable stationary part 51 and is then transferred to a destruction site so that infection through contamination can be avoided . the stationary part 51 will be completely free of any contamination and can be used repeatedly . the stationary part 51 can additionally contain sources of electric energy , electrical leads and it can also contain a unit for the control of pressure , temperature and time and suitable displays for visualizing the corresponding parameters . the embodiment shown in fig6 and 7 using only one syringe 13 for performing both filling and pulsating functions operates in a similar manner , although expanding the enclosure is performed by operating drive means 55 ′ to move the body or housing 23 of syringe 13 relative to the piston 33 and the bed 89 in an axial direction . after the expanding operation the body 25 of syringe 13 is maintained in a fixed position by bringing threaded element 71 in engagement with the threaded bar 65 , whereafter drive means 75 is started to perform the function of providing internal circulation in the same manner as the device shown in fig3 . fig1 shows an arrangement which constitutes an alternative to the embodiment shown in fig3 . this alternative drive means 75 is arranged on platform 33 , and syringe 13 of fig3 has been replaced by a device 36 comprising an elongate hollow body 32 and , attached at the rear end thereof outside of flange 45 , a bellows 46 which at its rear end in turn carries actuating plate or disc 41 . operatively , the device of fig1 operates in exactly the same manner as the arrangement described in connection with fig2 and 3 to provide for effective circulation in an internal flow circuit of liquid medium . in fig1 there is shown an arrangement which constitutes an alternative to the embodiment shown in fig1 , where syringe 13 of fig3 has been replaced by another device 38 . driving device 75 as shown in fig3 is not illustrated in fig1 except element 59 that has been modified to match new device 38 replacing syringe 19 . device 38 contains a hollow elongate body 34 having an exterior circumferential flange 45 engaging a slot in bed 57 in the same manner as shown in fig3 . at the rear end of body 34 there is arranged a flexible inelastic container 48 which is connected to element 59 of drive means 55 through a bar 50 having at its free end a ball 52 fitting into a recess 54 of element 59 . the device shown in fig1 can thus be used to replace syringe 13 shown in fig2 using the eccentric device of fig3 for providing reciprocation of element 59 resulting in internal circulation as previously described . in such pulsation , container 48 of fig1 moves between the position shown in full line and the position shown in dotted line at 42 . even if an indicated above there are alternative embodiments , wherein the syringe 19 and 13 according to fig1 have been replaced with other devices illustrated in fig1 and 11 , the embodiment according to fig1 involving syringe 19 is preferred . on the one hand , such syringes can be massproduced at a very low cost and , on the other hand , as already described such a syringe can easily be deairated and filled with liquid , respectively , through an operation well known to the operator . furthermore , syringe 19 can be graduated , such as with a milliliter scale , so that the operator will know the quantity of liquid injected into the system . when using drive means 55 ′ and 55 ′, according to what has bee described in connection with fig4 and 5 and fig6 respectively , fine adjustment of the system pressure can be made , and practice has also shown that this is necessary . as earlier described the distal section 5 of the device , the enclosure being in a collapsed condition , is inserted into the uterus cavity , piston 35 of syringe 19 being then pushed forward to expand the enclosure . as long as the expansion takes place without the walls of the enclosure touching the walls of the cavity the expansion takes place at a low pressure depending inter alia on the elastic properties and thickness of the material of the enclosure . as a rule a highly elastic , thin enclosure material is desirable in order to obtain maximum compliance with the irregular inside surface contour of the uterus cavity while offering at the same time efficient heat transfer from the liquid medium to the endometrium . to the extent that the enclosure in its expansion comes into engagement with the major part of the interior surface of the uterus cavity the resistance of the uterus muscle towards expansion will increase , the pressure in the system increasing at a higher rate for every volume of liquid injected . pressure versus volume is indicated in fig1 . curve 1 in full line shows said relation in the free expansion of a thin - walled elastic enclosure suitable for the treatment of uterus in accordance with the present invention . as seen from the figure a certain initial pressure ( about 70 mm hg ) will be required for a first small expansion ( about 1 ml ). then the expansion takes place at a slowly increasing pressure ( about 70 - 100 mm hg ) that can be designated the plateau pressure . as earlier mentioned the curve will take another shape when the enclosure is brought to expand in for example a uterus cavity . fig1 shows two curves a - c and b - d with dashed lines the pressure / volume relation with two different cavity sizes . as seen from the figure the curves increase quite steeply depending on the resistance of the uterus muscle . according to the invention it is intended to open the cavity by expansion of the enclosure so that the whole interior surface of the cavity will be subjected to heat treatment at the same time as the circulation of blood will be reduced so that a more efficient and deeply penetrating heat destruction can be obtained . however , it is important that uterus will not be subjected to an excessive pressure which can cause damage through tissue failure . it has been found that a suitable pressure lies within the range about 100 to 140 mm hg . higher pressures can be used but the pressure should not exceed abouth 170 to 180 mm hg . even if for example such a device for fine adjustement of the pressure as described in connection with fig4 will be used the steep increase in pressure at a small change of volume constitutes a problem , inter alia in view of the fact that the living muscle does not give a constant resistance . in certain cases strong contractions arise in the muscle , which could result in a drastic increase pressure if a rapidly acting pressure release cannot be provided . it is conceivable to arrange for servo control of the device for fine adjustment as described so that the pressure can be maintained between two pre - determined values , but such system is complicated and is not always rapid enough in order to compensate for for example muscle cramps . fig1 shows a pressure control device which in a simple and efficient manner provides for facilitated adjustment of pressure and enables pressure release upon sudden pressure increase resulting from for example contraction of uterus . said control means designated 101 has been added to = he the disposable part 7 shown in fig1 via a second side conduit 103 connected to side conduit 16 of the disposable part 7 . control device 101 contains a central tube 105 provided with holes 107 . said tube 105 is surrounded by an elastic balloon 109 which is thereby connected to the disposable part 3 so as to be filled with liquid when the system is filled using syringe 19 . when pressurizing the system elastic balloon 109 then expands , such as to the position 109 ′ shown in full line in fig1 . in accordance with the invention there is selected for balloon 109 an elastic material of for example silicon . the plateau pressure of said material is substantially higher than the plateau pressure for enclosure 23 but somewhat higher or equal to the pressure suitable for the treatment . the pressure / volume relation for a suitable material is shown in fig1 by curve 12 in dotted line . as is clear from fig1 the plateau pressure lies within the range about 180 to 200 mm hg . the system including pressure control device 101 is pressurized as described in connection with fig4 and 5 , but the pressure / volume relation will be different in view of the fact that also balloon 109 will expand during the pressure increase . fig1 shows how the pressure increase ac changes to ae and how the pressure increase bd changes to bf . the change obtained by adding the pressure control device 101 to the system results on the one hand in the advantage that the pressure increase within the range 80 to 150 mm hg is less steep , i . e . easier to control . on the other hand , the pressure increase at pressures exceeding about 160 mm hg is very slow . in this case a suitable operating pressure is about 150 to 160 mm hg . this means for example that at a sudden contraction of uterus the pressure increase from the pre - set pressure will be relatively small so that damages to uterus can be prevented . the reason as to why drastic pressure increase can be prevented is the fact that if enclosure 23 will be compressed through contraction of uterus a corresponding quantity of liquid will be transferred to balloon 109 . if the contraction of uterus ceases a corresponding quantity will be transferred back from balloon 109 to enclosure 23 . as is clear from the above description the supplementary equipment residing in pressure control device 101 is simple end and cheap in manufacture and belongs to the part of the equipment that is disposed of after use . in certain cases it can be of advantage to be able to vary the plateau pressure of the balloon 109 . this can be done by surrounding balloon 109 with an airtight container 111 shown by the dashed square in fig1 . container 111 can be provided with pressurizing means , such as a manual operated pump , not shown it fig1 . by pressurizing container 111 the plateau pressure of balloon 109 can be set at the desired value . in this manner different plateau pressures can be obtained using one and the same balloon 109 .
an apparatus for effecting hyperthermia in a narrow body cavity or duct including : a disposable first part having an elongate distal section intended to be inserted into the cavity or duct having a centrally located , heat - releasing element , which is either surrounded by an elongate housing or is itself constituted by an elongate housing , and a flexible and / or elastic enclosure surrounding the housing in a liquid - tight manner , further including a device for supplying energy to the heat - releasing element and an axially operating first inlet at the proximal part of the housing , an outlet from the housing being arranged for the supply of heat - transmitting medium under pressure for expansion of the flexible enclosure to accommodate and to exert a controlled pressure on surrounding walls of the cavity or duct , a second inlet to the housing , and medium - actuating device for the expansion of the flexible enclosure and for internal circulation of the medium through the housing ; and a permanent non - disposable second part having a drive for the device for expansion and for internal circulation , and a connection for releasably interconnecting the drive and the device means for expansion and internal circulation .