[ 0030 ] fig1 shows a wire body generally designated 1 in an embolization device shown in the predetermined unloaded shape . the wire body has a distal or front end section 2 formed as a spiral with a decreasing helix diameter in the direction of the front end 3 , and a helix - free section 4 connecting the end section 2 with a proximal or back end section 5 , the center line of which turns through an angle of about 340 ° compared with the substantially rectilinear course of the center line in the section 4 . the back end of the wire body has a coupling means 6 which may , for example , be formed as explained in connection with fig1 . the dimensions of the wire body depend on the vessel geometry at the site to be occluded . the largest helix diameter dd in the end section 2 typically corresponds to the diameter of the vessel lumen and may , for example , be of the same size or slightly larger than this lumen . the smallest helix diameter can be half or slightly over half of the largest diameter . the diameter dp in the helical portion of the back end section 5 may be comparable with or smaller than the largest helical diameter in the front end section 2 . the helix - free section 4 has a length substantially larger than the diameter of the vessel lumen , for example at least six times the size , which may typically provide at least four wire portions crossing the vessel lumen . the front end section 2 may , for example , have a largest external diameter in the range from 2 to 13 mm . the helix - free section 4 may , for example , have a length in the range from 30 to 1000 mm , and suitably in the range from 30 to 300 mm , if no measures have been taken to reduce the friction between the wire body and the inner surface of the catheter . finally the back end section 5 may have a largest external diameter in the range from 2 to 13 mm , suitably from 4 to 8 mm . if the vessel has a lumen of 2 mm at the site of occlusion , the end sections 2 and 5 may be pre - shaped with an external diameter of about 2 mm , and the section 4 may have a length of at least 20 mm , which renders it possible to have more than 10 wire passages across the vessel lumen . if the vessel has a lumen of 6 mm , the end section 2 may have a largest external diameter of about 6 mm , the end section 5 a diameter of about 5 mm and the section 4 a length of at least 50 mm . if a more dense occlusion is desired , the section 4 may be given greater length . the wire body 1 may , for example , be manufactured by helical winding of a thread around a mandrel . the thread may , for example , be of platinum , palladium silver , gold , nitinol , stainless steel , alloys of these materials or of a springy plastic , such as modified butadiene . platinum is the preferred material owing to its great radiopacity . the thread diameter is adapted to the diameter of the wire body and the desired rigidity of the wire body and may , for example , in the range from 0 . 02 to 0 . 2 mm , preferably from 0 . 04 to 0 . 1 mm . at superselective applications , such as intracranial or renal occlusion , occlusion in the liver or in vessels at joints or bones , the thread may advantageously have a diameter in the range from 0 . 35 to 0 . 45 mm . along the main part of the length of the wire body the thread may be spun at a pitch corresponding to the thread thickness so that the windings touch each other . this increases the compressive strength of the wire body , which is a particular advantage if the wire body in its extended shape is very long so that noticeable friction has to be overcome at its advancement through the catheter . for the same thread thickness the rigidity of the wire body decreases with increasing diameters of the body . the wire body may typically have an external diameter in the range from 0 . 0254 mm ( 10 mils ) to 1 . 016 mm ( 40 mils ), preferably from 0 . 0254 mm to 0 . 457 mm ( 10 - 18 mils ). if the site of occlusion has a very small lumen , the diameter may be chosen to be smaller than 0 . 0254 mm . after spinning of a straight coil piece , a piece thereof is cut off in a length corresponding to the extended length of the wire body . then the end sections 2 , 5 can be deformed around a mandrel to the desired shape . finally , the wire body can be heat - treated in an oven in a well - known manner . if the section 4 is longer than the length of the oven chamber , it is necessary to wind the whole wire body 1 together into a coil size capable of being accommodated inside the oven . after the heat treatment of such a body , the section 4 may retain the wound shape in which the diameter of the windings is much larger than the diameter of the end sections 2 , 5 . when the section 4 in the present connection is characterized as being helix - free this means that the section has no helices of a diameter comparable with the vessel lumen at the site of placement . thus , for manufacturing reasons the helix - free section 4 may have been given a winding - forming curved shape , the winding diameter being at least 10 - 25 times larger than the vessel lumen at the site of placement . in the following description of other embodiments the same reference numerals will be used for components of the same sort as in the above embodiment for the sake of simplicity . the embodiment shown in fig2 also comprises a wire body 1 with a front end section 2 being spiral - shaped , and with a helix - free section 4 , but the end section 5 ′ is here formed as an approximately rectilinear extension of the section 4 . the embodiment is simpler to manufacture because the end section 5 ′ does not have to be pre - shaped in a curved shape . this is possible if the coupling means 6 is of a type that cannot damage the vessel wall by direct abutment with it , for example if the coupling means is spherical for engagement with a holder at the end of the guidewire , or if the back end of the wire body 1 is gripped by an inflatable member at the end of the guidewire . the embodiment shown in fig3 is particularly applicable for occlusion of aneurisms . the embolization device here comprises a wire body 1 with a helix - free middle section 4 , a front end section 2 ″ and a back end section 5 ″. the center axis of the front end section 2 ″ turns through an angle of about 130 °, which ensures that the front end of the wire body cannot meet the vessel wall directly when advanced into the aneurism . the center axis of the back end section 5 ″ turns through an angle of about 210 °, which ensures that the coupling means does not touch the vessel wall when the device is fully placed in the aneurism . [ 0037 ] fig1 shows an embodiment suitable for occlusion at two or more mutually separate sites in a vessel . the device comprises a wire body 1 having at least two helix - free sections 4 , a front end section 2 formed similarly to those in fig1 and 2 , and a back end section 5 ′ formed as in fig2 . the helix - free sections are mutually connected via intermediate sections 7 which in the predetermined shape have helical courses with an external diameter in the windings corresponding to the lumen of the vessel . to achieve a suitable occlusion at the site of placement , the helix - free section ( s ) 4 preferably has / have an aggregate length of at least 90 mm , suitably a length in the range from 100 to 700 mm . [ 0038 ] fig1 shows an example of a coupling means 6 intended for screwing into a thread 8 at the distal end of a guidewire 9 . the thread on the guidewire has been provided by fixing the windings 10 in a protective coil 11 at a pitch slightly larger than the diameter dt of the thread 12 of the wire body . the coupling means 6 has been provided by axially pulling out the windings 13 of the back end of the wire body until they display a pitch corresponding to the pitch in the thread on the guidewire . the other known types of coupling means are also applicable . if it is not necessary to be able to reposition the embolization device in the catheter , it can , instead of being mounted on a guidewire , be discharged from the catheter by means of a stylet - shaped pusher not connected with the wire body , but only pushing it forwards through the catheter . the different above curvatures in the front section of the wire body constitute a kind of guide means which is an integral part of the wire body and prevents the front end of the wire body from damaging the vessel wall when it is pushed out from the catheter . the front end section 2 ′″ may alternatively have a center axis being a rectilinear extension of the center axis of the section 4 , and in that case the front end of the wire body may be provided with a separate guide means 14 , which may , for example , have the design shown in fig1 . the guide means 14 is umbrella - like with a front dish - shaped screen 15 of a thin and springy material , such as nitinol , platinum or plastics . via several thin struts 16 the screen 15 is placed in engagement with the end section of the wire body so that the screen lies protectively in front of the end of the wire body . the screen has a relatively large radius of curvature , preferably of at least five times the external diameter of the wire body . this means that firstly the screen distributes the abutment pressure of the front end on the vessel wall over a suitably large areal , and secondly it makes the front end turn to the side at continued pushing out of the wire body from the catheter so that the front end section nestles along the vessel wall and is frictionally locked to it in the manner described above . as the struts 16 are thin and the screen is located in front of the end of the wire body the screen will lie folded together in front of the wire body when it is advanced through the catheter , which renders possible advancement through a catheter with the same internal lumen as the catheters used for the above embodiments . clearly , details of the above embodiments can be combined for the provision of new embodiments , and at least the front end section 2 can also have a helical shape with windings of a substantially constant external diameter . the intermediate section 7 shown in fig1 may alternatively have a spiral shape . now placement of the embolization device in an aneurism 17 will be described in detail with reference to fig4 - 7 . an introducer catheter 18 is advanced percutaneously and transluminally in a well - known manner along a suitable path until the distal opening 19 of the catheter is located in the neck of the aneurism as shown in fig4 . then a guidewire mounted with the embolization device is inserted into the catheter and pushed forwards until the front end section 2 ″ meets the vessel wall , whereupon the end section at continued pushing out is automatically guided by the curvature of the end section towards abutment with the vessel wall in a frictionally locking manner . fig5 shows the situation where the frictional locking has been established . at the continued pushing out , the helix - free section 4 in front of the catheter opening 19 curves into a direction towards the middle of the aneurism and further towards the opposite vessel wall where frictional locking also takes place as shown in fig6 . a portion 20 of the section 4 thus crosses the aneurism and at either end is locked to the vessel wall . at the continued pushing out this sequence repeats itself , the section 4 after each frictional locking to the vessel wall again seeking towards the middle of the aneurism and finding another abutment place on the opposite vessel wall . fig7 shows the situation immediately before the whole wire body has been placed , and it can be seen that the helix - free section has assumed a complexly curved shape in which the curvatures of the section vary continuously and without breakpoints that might cause a local overload of the vessel wall , and that the resulting course of the section 4 causes the aneurism to be crossed by many wire portions . [ 0042 ] fig8 - 10 illustrate the placement of an embolization device in a vessel 21 with a healthy vessel wall , but where it is desired to occlude the vessel itself . first the catheter 18 is introduced as mentioned above , and then the embolization device is advanced , and the front end section 2 is pushed out through the catheter opening 19 and assumes its predetermined shape , the end section lying frictionally locked to the vessel wall as shown in fig8 . then the catheter is retracted slightly to the position shown in fig9 where the section 4 has a free length between the section 2 and the catheter opening so that the column loading in the wire body makes the released part of the section 4 curve to the side at the continued pushing out . the section 4 will then in a similar manner as that described above meet the vessel wall and be frictionally locked to it , whereupon it will seek towards the vessel center and onwards for frictional locking on an opposite area of the vessel wall , and so forth until the whole wire body has been placed . fig1 shows the partially occluded vessel before conclusion of the placement , and fig1 shows the vessel after concluded placement of an embolization device having a section 4 of large length . it is directly seen that the many vessel - crossing wire portions produce an extremely efficient occlusion of the vessel , particularly at its center , where prior - art embolization coils have not been able to produce a sufficiently efficient occlusion to be able to avoid recanalization with any suitable degree of certainty . because the section 4 places itself across the vessel to be occluded , the occlusion can be performed solely by means of the wire body . thus there is no need to use the formerly known occlusion hairs of silk or dacron to occlude the vessel center . this means that the embolization device according to the invention , when it is free of occlusion hairs , can be inserted through a catheter with advantageously smaller inner lumen than the known embolization coils with hairs because no space is required inside the catheter for the hairs . as these hairs also generate an unfortunate , high friction between the coil and the inner surface of the catheter , the device according to the invention is easier to advance through the catheter . this can be utilized to place wire members of a greater length and / or of lower rigidity . if a further advantageous reduction of the friction is desired , the inner surface of the catheter or possibly the wire body itself may be coated with a friction - reducing coating , such as a ptfe coating or a hydrophilic coating . naturally it is possible within the scope of the invention to provide the wire body with occlusion hairs , but it is not preferred for the above reasons . a number of experiments have been carried out to find suitable rigidities of section 4 of the wire body so that it obtains the desired vessel - wall seeking rigidity without becoming so stiff that the outward pressure on the vessel wall becomes too high . the experiments were carried out with helically wound platinum threads for different thread diameters d and for different external diameters d of the wire body , i . e ., external diameters of the helical windings . for each geometrical set five experiments were carried out in which a coil piece 50 mm long was clamped in holders in a stretching apparatus whereupon the holders were pulled apart to an extension e = 10 mm , and the tensile force p required for this was measured . on this basis the spring constant c = p / e was calculated . the result of this is reproduced in the below table 1 . the threads were subsequently pushed at right angles on to a plane surface to see whether the curving out took place in the desired manner . it turned out that the length of the free portion outside the catheter opening was important to the force exercisable on the plane surface . with a coil of d = 14 mils and a thread thickness of d = 0 . 075 mm and a projecting length of 5 mm a pressure of about 2 g could be measured , while with a projecting length of 20 mm no pressure could be recorded by the measuring apparatus used . when the spring constant is lower than 0 . 0008 n / mm , the coil no longer had a sufficient vessel wall seeking property . it has been mentioned that section 4 may be completely straight in the predetermined shape . as the wire body 1 may be of great length and of a small diameter , it may be difficult at placement of the wire member on a plane surface to achieve a straight shape because there will be a certain friction against the supporting surface . if , instead , the wire body is suspended at the transition between the helix - free section and one of the end sections , the predetermined shape will appear clearly , and section 4 will hang down vertically without any curvature .