DYNAMIC SELF-LOCKING STEM FOR HIP PROSTHESIS

Abstract: The stem for joint prostheses, in particular for hip prosthesis, has a proximal neck region (1), a lateral tension region (2), a medial compression region (3) and a central region (4) lying between said lateral and medial region (2, 3). Said central region (4) is provided with a regular pattern of anteroposterior cuts (5) extending from said proximal region (1) to the distal end (6) of the stem rendering the stem stiffness adaptable to the stiffness of the receiving bone cavity.

Description: DYNAMIC SELF-LOCKING STEM FOR HIP PROSTHESIS This invention relates to a stem for joint prostheses, in particular for hip prosthesis, having a proximal neck region,a lateral tension region, medial compression region a central region lying between said lateral and medial region. Prosthetic loosening remains a major complication in the replacement of joints, testifying to the still unresolved problems of interfacing load bearing implants to living bone. Necessary conditions for sound long-term anchorage of a joint prosthesis are: - appropriate load transfer between the prosthesis and bone; and - a motion-free interface between the prosthesis and bone. Bone as a living tissue sets these conditions which must be respected in the design of prosthetic devices. Femoral component anchorage in hip joint replacements by a stem has probably been responsable for their generally superior performance to any other prosthetic component to date. Elimination . of bone cement from the stem anchorage makes the above requirements even more critical and more difficult to fulfill even in this rather simple rod-in tube configuration. Summary of the Invention The invention as claimed solves the problem of how to desing a dynamic self-locking stem for a joint prosthesis capable of "adapting its stiffness to the stiffness of the surrounding bone tisse. The stem according to the invention is unique in that - it has a structure to facilitate load transfer from prosthesis to bone; - it has a mechanism to ensure a motion free interface to bone; - it is adaptive and will accomodate the unavoidable bone response to the new mechanical environment. The advantages offered by the invention are the result of the design modifications within the stem in contrast to the conventional surface changes on the stem of most state of the art prosthesis. Each of the medial and lateral regions can be shaped and sized appropriately for its function, allowing gradual load transfer to bone, i.e. the compliance of said medial an lateral regions can be fully matched to that of bone cortices. This provides the basis for the structural design, whereas the segments between said lateral and medial regions are used to control the interface stresses. The connections between said medial/lateral regions and said segments consist of very thin flexible bridges that act as hinges. Inclination of the segments with respect to the stem axis determines the amount of >*_ stem widening that occurs with loading. With physiological loading the lateral region tends to move proximally as the medial region moves distally and the segments turn so as to increase the separation of the medial/lateral regions. The optimal design criterion calls for stem widening at all levels producing sufficient normal interface stress to prevent any movement due to shear stress. This guarantees absolute dynamic stability at the bone-prosthesis interface. The bending stiffness of the stem depends on the amount of shear coupling provided to the medial and lateral regions of the stem by bone. Assuming a stable bone-prosthesis interface, the stiffness of the stem will increase with the increase in stiffness of surrounding bone. Modulation of stem stiffness by bone stiffness plays an important role in bone reaching an " equilibrium state following stem insertion. Any stem will "stress shield" some bone within the load transfer zone. Generally, a higher stem stiffness/bone stiffness ratio results in more stress shielding. This results in reduced bone stiffness, amplifying the stress shielding effect. The result of this positive feedback process would be total stress shielding of affected bone. The stem stiffness modulation by bone avoids this effect since reduced bone stiffness caused by stress shielding will also soften the stem. In addition to the unique features discussed above, the stem according to the invention offers an important practical advantage of immediate stability. At insertion the stem is hammered-in through an anvil directing the insertion force latero-distally. This causes the stem to reduce the width and elastically preload the interface with the bone. This preload will eventually be released through bone .remodelling and will not provide lasting stability. This preload allows bone apposition against the stem and thus improves the quality of fit. Good fit between the stem and bone is required for the locking mechanism to function as described above. The various features of novelty which characterize the invention are pointed out with particularity in the claims annexed to and forming part of this disclosure. For the better understanding of the invention, its operating advantages and specific objects attained by its use, reference should be had to the accompanying drawings and descriptive matter in which are illustrated and described preferred embodiments of the invention. Brief Description of the Drawings In the drawings: Fig. 1 is an antero-posterior view of a stem according to the invention. Fig. 2 is an enlarged sectional view of the middle segment of the stem according to Figure 1. Description of the Preferred Embodiments Fig. 1 represents a stem according to the invention. Lateral region 2 of the stem is separated from the medial region 3 by a multitude of full-thickness cuts 5 running down the middle region 4 of the stem from the proximal region 1 out to the distal end 6 of the stem. Cuts 5 are preferably produced by spark erosion wire cutting. Fig. 2 represents an enlarged middle segment of the stem according to Figure 1. Tension transferring lateral truss 2 and compression transferring medial truss 3 are separated from the middle region 4 by sections of the cuts 5 running along lines 8 and 9 respectively. Thin flexible hinges 7 are connecting segments 10 to the trusses 2 and 3. The line connecting the hinges of one segment is inclined with respect to the transverse axis by an angle α, which is comprised between 20° and 40°, preferably between 25° and 35°. A cutting wire is inserted through the holes 11 and then guided for cutting along a Z-shaped trajectory 5.

Claims: Claims 1. Stem for joint prostheses, in particular for hip prosthesis, having a proximal neck region (1),a lateral tension region (2),a medial compression region (3),a central region (4) lying between said lateral and medial region (2,3), characterized in that said central region (4) is provided with a regular pattern of anteroposterior cuts (5) extending from said proximal region (1) to the distal end (6) of the stem rendering the stem stiffness adaptable to the stiffness of the receiving bone cavity. 2 . Stem according to claim 1 characterized in that said cuts (5) are arranged in such a way that a series of flexible hinges (7) are formed along the bounderies (8,9) of said lateral and medial regions (2,3) with said central portion (4) of the stem allowing movement of the mediolateral segments (10) formed by said cuts (5) . 3. Stem according to claim 1 or 2, characterized in that.said cuts (5) are in the shape of a Z. 4. Stem according to one of the claims 1 to 3 , characterized in that the angle α, formed by the line connecting the hinges (7) of one segment (10) and the transverse axis of the stem, varies along the stem producing sufficient compression between the stem and bone to prevent movement at the interface. 5. Stem according to claim 4, characterized in that said angle , α is comprised between 20 and 40°, preferably between 25° and 35°. 6. Stem according to one of the claims 1 to 5, characterized in that the distance between said hinges (7) in proximodistal direction is comprised between 6 to 10 mm, preferably between 7 to 9 mm.

Inventors: TEPIC SLOBODAN, TEPIC, SLOBODAN
Applicants: EXPERIMENTELLE CHIRURGIE LAB, LABORATORIUM FUER EXPERIMENTELLE CHIRURGIE, FORSCHU
Application year: 1987
Main classification: A61F2
IPC codes: A61F2