the following description is given primarily with reference to a procedure for determining the relevant geometric parameters and for implanting a hip socket , but reference is additionally made also to the determination ( relatively independent thereof ) of the relevant geometric parameters and the implantation of a stem component as the second component of an artificial hip joint . the operating surgeon , when planning a hip joint implantation , needs to determine the following values for the socket : the two angles of alignment of the socket axis relative to the body planes are here selected on an x - ray image by the operating surgeon in accordance with medical standpoints . these angles can likewise be modified by the operating surgeon intra - operatively . 3 . angle in the sagittal body plane between vertical axis and the direction from the iliac crest to the symphisis . determining this angle allows intra - operative determination of the body axes and thus of the plan coordinate system . it is assumed that the patient is supine at the beginning of the operation ; the physician has an x - ray image available which gives an adequate picture of the overall anatomical situation and the nature of the bones and from which he makes his first deductions as to the size of implant to be installed and the preferred approximate alignment of the implant . an incision , 4 cm in length , is made 3 - 5 cm dorsally of the spina iliaca superior anterior , the iliac crest is exposed and the tissue is exposed with a rasp . fig1 shows an iliac crest locator 1 with an associated mounting clamp 3 , which is attached in the exposed region of the iliac crest . the mounting clamp 3 comprises a medial clamp component 3 . 1 and a lateral clamp component 3 . 2 , which are screwed together by means of an allen bolt 5 until the mounting clamp is firmly seated on the iliac crest . the actual iliac crest locator 1 has a sickle - shaped basic body 1 . 1 having a mounting sleeve 1 . 2 for positioning on the mounting clamp 3 as well as a 4 - point locator array 1 . 3 consisting of four ir - reflecting spheres each of which is partially surrounded by a diffuser ( not separately referenced ) in the shape of a spherical segment in order to avoid troublesome radiation effects . these are so - called passive targets or adapters which are known per se and the mode of operation of which in conjunction with the ( likewise known ) stereocamera arrangement of a so - called navigation system will therefore not be described in greater detail here . after being put in position , the locator 1 is rotated relative to the mounting clamp 3 so that the locator array is suitably aligned relative to the camera but without any of the reflecting spheres being masked by another one . then , by screwing the locator and the mounting clamp together , a rigid connection is established between the two . instead of being attached to the iliac crest , the multipoint transducer 1 , referred to as the iliac crest locator above , can also be attached to the roof of the aceta - bulum of the pelvis . this has the advantage that the above - mentioned ( additional ) incision in the region of the iliac crest becomes superfluous , but the attachment of the multipoint transducer , which is then referred to as the “ surgical field locator ”, is less stable if the bone structure is weak . fig2 shows , in addition to the above - described bone - fixed locator 1 , a manual sensor 7 having a rod - shaped sensing component 9 , which tapers towards one end and from which a holder 9 . 1 projects perpendicularly , an approximately y - shaped sensor body 7 . 1 and a 4 - point locator array 7 . 2 , similar to the structure of the iliac crest locator described above . the locators of the components of the arrangement described below are also of similar structure , so that the naming of the corresponding parts and portions of those locators and the description thereof will be omitted . using the manual sensor 7 , at the beginning of the navigation sequence various points on the plane of the operating table on which the patient is lying are scanned in order to determine the position of the table plane in space . although this is not required for the actual determination of the patient &# 39 ; s position , it can be used for plausibility considerations ( for example in respect of the significance of the inclination of the patient &# 39 ; s pelvis relative to the plane of the table etc .). for the actual navigation it is usually assumed that the patient &# 39 ; s frontal plane lies parallel to the plane of the table . then , using the manual sensor 7 , characteristic bony references in the pelvis region are sensed through the skin . first of all , the left and right iliac crests and the center of the symphysis are sensed . these three sensed points and the crest / symphysis angle ascertained during the planning enable the body axes to be clearly determined . the direction from left iliac crest to right iliac crest represents the transversal body axis . the direction from the center of the iliac crest points to the symphysis is rotated through the crest / symphysis angle about the transversal axis and thus represents the vertical body axis ( orthogonal to the transversal axis ). the sagittal body axis is obtained from the two first - mentioned axes as an orthogonal . fig3 shows , in addition to the iliac crest locator 1 , a femur locator 11 having an associated adapter ( femoral clamp ) 13 for attachment close to the proximal end of the femur . the femoral clamp 13 has a two - part body consisting of a first base member 13 . 1 , which is fork - shaped in plan view and approximately l - shaped in side view , from which two pins 13 . 2 project for mounting the locator , and a second base member , which is approximately l - shaped in side view and which can be locked together with the first base member 13 . 1 . the structure of the femur locator 11 itself , apart from having an angled locator rod , is substantially the same as that of the iliac crest locator . it is pushed by way of a mounting sleeve 15 . 1 at the free end of a locator rod 15 onto one of the two pins 13 . 2 of the femoral clamp 13 . the femoral clamp 13 is then attached to the mounted locator rod 15 on the lateral femur side approximately at the level of the trochanter minor or between the trochanter minor and the trochanter major , by pushing the muscle groups located there aside and inserting the clamp . the rotated position is to be so selected that the locator rod projects laterally out of the surgical field , if possible in the direction of the camera . then the clamp is tightened with a moderate torque , the actual locator array ( not separately referenced here ) is mounted and aligned towards the camera and finally the femur locator is screwed tight . the kinematic center of rotation of the hip is then determined both in the hip - fixed coordinate system and in the femur - fixed coordinate system by a plurality of relative measurements of the femur locator in the hip - fixed coordinate system with the leg in different positions . the transformation of all measured values can accordingly be effected from the hip - fixed coordinate system into the coordinate system of the body axes . accordingly all the calibrated tools can then be aligned relative to the body axis coordinate system ; in this connection see below . using the center of rotation as origin , the implant can be installed at its kinematic origin . should corrections be necessary , displacements and changes of angle in the plan can be carried out intra - operatively . once the operating surgeon has carried out the position recordings in the various positions of the leg in “ dialogue ” with the interactive user guidance ( error correction again being provided on the basis of plausibility calculations ), the femur locator is removed from the clamp 13 and the head of the femur is resectioned . the diameter of the resectioned head is measured and , on the basis of the measurement result , a suitable hemisphere is selected for the next step , namely the determination of the center of the acetabulum or geometric center of rotation of the hip . as shown in fig4 , the selected hemisphere 17 is combined with a manual sensor 7 ′ of the kind shown in fig2 and described above to form a sphere adapter / manual sensor combination 19 . by guiding such a locator into the socket region ( usually assuming a certain anteversion angle , e . g . 12 °), first the validity of the ( kinematic ) center of rotation determined by means of the femur locator is checked from the geometric point of view and secondly the results allow a “ cross - check ” of the planned implantation values from geometric standpoints . furthermore , moving the hemisphere 17 in the socket region provides pointers to possible mechanical collisions . the structure of the half - shell and its adaptation to the manual sensor ensures that the probe tip is always in the sphere center of the sensing hemisphere . there then follows , within the framework of the stored evaluation program with interactive user guidance , the final planning of the implantation , from the determination of the implant size that is to be installed through to displacement values and angle sizes . on that basis and with reference to previously entered specific instrument data , the system calculates desired positions for the resectioning and setting instruments to be used or , more specifically , for their operational parts . fig5 shows , in addition to the iliac crest and femur locators 1 , 11 , a milling tool / locator combination 21 having a milling shaft 23 , a milling shaft adapter 25 and a locator 27 , the structure of which corresponds substantially to that of the femur locator 11 according to fig3 . this instrument is aligned in a socket region in the manner likewise shown in the figure , the position and alignment being recorded on the basis of position signals from the locator array and being displayed visually on screens in the manner shown in fig6 . a milling tool position that is correct in accordance with the plan data is indicated on the display by a ring encompassing the milling shaft and by acoustic signals . as soon as a socket seat has been produced in accordance with the plan data , the milling tool / locator combination is converted into a setting instrument / locator combination 29 , as shown in fig7 , the locator 27 again being used but this time in conjunction with a setting instrument shaft 31 and a shaft adapter 33 . using this instrument , a hip socket 35 is set in place in a manner that is largely analogous to the manipulation of the milling tool / locator combination and that is likewise displayed on the pc screen . the ultimate position of the hip socket 35 is still to be entered into the system by the operating surgeon . then the stem preparation and implantation ( in the first instance a test stem ) are carried out , either in a conventional way or again assisted by the navigation system . height and anteversion of the stem are fixed with reference to the plan data ; only the ball neck length is still freely selectable . the joint is then assembled with the test stem , and stability and any potential for collisions during movement of the stem in the socket are tested . in addition , the leg length is roughly tested by comparing the position of the malleoli on the leg undergoing surgery and the healthy leg . if joint stability problems arise , a solution is sought by selecting a specific ball or a stem of a different size from an available range . optionally , in this phase it is also possible to take measurements of the other leg using the navigation system , the results of which can be used in the sense of symmetry considerations with a view to fine adjustment of the implant . it will be understood that for such measurements , instead of using the femur locator described above , there is used a femur locator modified for external mounting over the skin . a considerable advantage of the proposed system is that using navigation data it is also possible to make a “ before and after ” comparison of the leg lengths ( on the diseased hip prior to the operation and during the above - mentioned testing step in the final phase of the operation ). for this purpose , the femur locator is again positioned and fixed in place on the holder which has remained on the femur and the position with the leg extended and aligned parallel to the longitudinal axis of the body is recorded . the position data obtained indicate any lengthening or shortening of the leg and also the so - called lateralization or medialization , that is to say the “ sided ” position of the femur . where too much metallization ( displacement towards the inside ) is indicated , a stem different from the test stem can be used in conjuncttion with a different ball ; in any case , however , the measured values suggest to the physician what should be taken into consideration in the further care of the patient . the following remarks relate to the use of the described system in stem preparation and implantation . the placement of the stem of a prosthetic hip requires the establishment of a planned antetorsion angle of the femur neck and the creation of the angle of the original leg length . the axial alignment of the stem is governed to a very great extent by the position of the medullary canal in the femur . as a result , it is only therefrom that the actual stem size or its offsets can be calculated . a calibrated awl is used to determine the medullary canal of the femur . a further important item of information for the placement of the stem is the determination of the center of rotation ; see above in this connection . fig8 shows a further component of the proposed arrangement that is suitable for use in this connection , namely a medullary canal awl / locator combination 37 having a medullary canal awl 39 , an awl adapter 41 and ( again ) a locator 27 , similar to the locator variant already shown in fig3 . for the insertion of this navigation instrument , the proximal femur end is opened with a box chisel or a piercing saw in the vicinity of the trochanter major and the medullary canal awl 39 is inserted therein from the proximal end . the angle of inclination and antetorsion angle of the head of the femur are determined pre - operatively from an x - ray image and are entered intra - operatively . in addition , the antetorsion angle can be determined intra - operatively by measuring landmarks on the knee joint and on the ankle joint , so that the body planes are known intra - operatively . the actual implantation angles and positions of the socket navigation can also be taken into account in the stem implantation . the last spatial position of the socket can be applied as a relative correction of the stem . this procedure ensures optimum implantation . the preparation of the femur for installation of the stem is then effected — analogously to the preparation of the socket seat with a navigated milling tool — with a navigated stem rasp , that is to say a stem rasp / locator combination , which is very similar to the combination shown in fig8 and is therefore neither shown nor described in greater detail here . after the preparation , a test stem is again inserted and the tests described above in connection with the socket - side navigation are carried out . when satisfactory results have been obtained , the final stem is then installed without it having to be navigated again . the invention is not limited to the arrangement described above and the procedure outlined in connection therewith , but can also be realized in modifications that lie within the scope of technical action .
arrangement for the intra - operative determination of the spatial position and angular position of a joint replacement implant , especially a hip socket or shoulder socket or an associated stem implant , or a vertebral replacement implant , especially a lumbar or cervical vertebral implant , using a computer tomography method , having : a computer tomography modeling device for generating and storing a three - dimensional image of a joint region or vertebral region to be provided with the joint replacement implant , an optical coordinate - measuring arrangement for providing real position coordinates of defined real or virtual points of the joint region or vertebral region and / or position reference vectors between such points within the joint region or vertebral region or from those points to joint - function - relevant points on an extremity outside the joint region or vertebral region , the coordinate - measuring arrangement comprising a stereocamera or stereocamera arrangement for the spatial recording of transducer signals , at least one multipoint transducer , which comprises a group of measurement points rigidly connected to one another , and an evaluation unit for evaluating sets of measurement point coordinates supplied by the multipoint transducer and recorded by the stereocamera , and a matching - processing unit for real position matching of the image to the actual current spatial position of the joint region or vertebral region with reference to the real position coordinates of the defined points , the matching - processing unit being configured for calculating transformation parameters with minimalization of the normal spacings .