making reference to the figures , preferred embodiments of the present invention will be described in detail . fig1 - 4 illustrate a preferred embodiment of the present invention in which a prosthesis generally indicated as 10 of unitary construction is illustrated . prosthesis 10 includes a stem section generally 20 and a ball section generally 30 of unitary construction therewith and extending outwardly therefrom at a proper angular relationship according to the anatomical characteristics of the relationship between the femur and the hip joint . stem section 20 basically includes a buttress section 22 , a middle section 24 and a distal section 26 . ball section 30 includes a ball 32 , a neck 34 located distal to ball 32 , and a collar 36 that is juxtaposed to buttress section 22 and extends laterally outwardly therefrom . collar 36 includes a shoulder or distal surface 37 along the underside of same that extends outwardly from stem 20 for engagement with the osteomotized surfaces of the calcar bone . an inferior side of buttress section 22 of stem 20 is relieved from a point adjacent distal shoulder surface 37 of collar 36 to medial section 24 , and a compressible material 40 is provided therein . compressible material 40 follows the general contour of stem 20 and is adequate in thickness such that when the prosthesis 10 is implanted , persistent proper contact is maintained between the shoulder 37 of collar 36 and the calcar bone c . making particular reference to fig1 it is seen that the side of stem 20 opposite ball 32 is straight along its entire length , while likewise making reference to fig2 it is seen that the lateral sides of stem 20 are straight along their entire lengths . the inferior side of stem 20 , however , deviates from a straight configuration only as necessary to extend angularly outwardly from a major axis thereof for proper support of ball section 30 , which extensions defines buttress section 22 . this particular stem configuration of a generally straight , smooth surfaced prosthesis stem is provided to minimize &# 34 ; wedging &# 34 ; of the prosthesis once implanted within the femur . furthermore , compressible material 40 , while ensuring proper contact with the calcar , also due to its compressible nature assists in minimizing wedging of prosthesis 10 . as shown in the figures , stem 20 of prosthesis 10 is devoid of any holes , fenestrations , indentations or the like , and presents a smooth outer surface . in fact , stem 20 is preferably polished to a mirror finish . when implanted in the femur f , stem 120 is surrounded by luting agent l such as bone cement ( see fig6 ). with the outer surfaces around stem 120 smooth and straight , and preferably highly polished , a minimum of shear stress is transmitted from the prosthesis across the prosthesis - luting agent interface i . the danger of cracking of the luting agent is thus minimized , leading to prolonged implanted life of the prosthesis . additionally as is illustrated in fig1 and 5 , a compressible material 45 is preferably received about the distal tip 27 of the prosthesis 10 , such that a minimum of axial compressive stress is transmitted from the distal tip 27 of the prosthesis to the luting agent surrounding same when implanted or to the femur , per se . while the compressible material 45 , 245 is illustrated in fig1 and 5 , fig6 illustrates a further embodiment of a means for avoiding such transmission of axial compressive stress . in fig6 a receiving element or sleeve 150 is provided about the distal tip 127 of the prosthesis stem 120 and defines an elongated opening 152 therewithin , into which distal tip 127 resides . receiving element 150 is secured within the femoral cavity and itself is surrounded by an appropriate luting agent l . the cross section of opening 152 within receiving element 150 closely approximates the cross section of the distal tip 127 of stem 120 such that a light frictional engagement therebetween is realized . in such fashion , luting agent l is precluded from entering receiving chamber 152 around stem tip 127 . with the arrangement as illustrated in fig6 should the calcar bone resorb , abrade or deteriorate adequate that prosthesis subsidence is permitted axially within the femur , distal tip 127 will simply move further within receiving chamber 152 without transmitting the adverse axial compressive stresses to the luting agent and thus to the femur , whereby again , prolonged implant life is achieved . chamber 152 may contain a closed cell compressible material such as polyurethane foam or one of the biocompatible resilient material set forth hereinafter or which will absorb axial force which precluding the ingress of body fluids therein . fig5 illustrates a further embodiment of a prosthesis generally 210 according to the present invention which is constructed quite similarly to the prosthesis as illustrated in fig1 - 4 , with the exception that the ball 232 of ball section 230 is smaller than as depicted in fig1 and 2 . the prosthesis illustrated in fig5 is thus intended for use in conjunction with an acetabular cup ( not shown ) that will also be implanted during a total hip arthroplasty . a prosthesis according to the present invention is suitable for surgical replacement of the head alone or as part of a total hip replacement . once implanted , the prosthesis enables a preponderance of the load carried by the hip to be transferred directly to the calcar region of the femur as axial compressive stresses in a stress distribution that closely simulates the stress distribution in a normal , healthy femur . resorption of the calcar bone and consequential prosthesis loosening are thus retarded and luting agent stress are reduced . particularly , the head or ball section of the prosthesis may be of any particular size and shape that is intended for use in hemiarthroplasty surgery or in total hip replacement surgery , with the ball section attached to the neck at any angle or degree of inclination consistent with anatomical limitations and surgical requirements . in like fashion , the neck may be offset or inclined at any angle to the axis of the prosthesis stem consistent with anatomical limitations and surgical requirements . the collar portion of the ball section is juxtaposed to the buttress section of the stem and is inclined to the axis of the stem in order that it may firmly contact the medial cortical margin of the neck osteotomy surface when the stem is inserted in the reamed intermedullary cavity . the collar is the principal structural element of the prosthesis of the present invention , and accordingly should be of adequate thickness so that it can safely support the applied loads throughout the service life of the implant . fairing of the collar into the neck of the ball section should be limited only by the range of motion needed for the joint and by the requirements of joint stability . the prosthesis , per se , may be fabricated from any suitable material that exhibits adequate strength and biocompatibility for the purpose of the implant . the high technology metals that are conventional in the manufacture of prostheses are preferred , and as mentioned above , the stem of the prosthesis should not contain holes , fenestrations , grooves or other irregularities that could serve to transfer shear load to the luting agent or to the appositional bone that may develop at any point below the collar - calcar contact . additionally , all surfaces of the stem should preferably have a mirror polish to minimize load transfer across the prosthesis - luting agent or prosthesis - bone interfaces . suitable materials for the prosthesis include stainless steel alloys , cobalt - chromium alloys , titanium alloys , and the like , aluminum oxide , ceramics , carbon , polyacetal , polysulfone and other high strength polymers , especially those reinforced with a strong second phase such as graphite fibers . the compressible material 40 located along a portion of the inferior surface of the buttress section of the stem and the distal tip of the stem may be manufactured of a suitable resilient , biocompatible material as exemplified by silastic rubbers , polyurethane rubbers , polyethylenes , polypropylenes and the like . such likewise could be reinforced with fibers or polymer particles . such could also contain fully enclosed pores that were filled with air or other highly compressible gas to increase the bulk compressability of the material . these pores would be completely embedded within the solid material and would not communicate with the surface . compressible materials 40 may be attached to the prosthesis in any desired fashion , such as mechanical fixation by interdigitation of the compressible material with suitable grooves , notches , protrusions or the like in the prosthesis surface or by direct chemical bonding with a suitable adhesive . the following examples validate the thesis of the improved prosthesis according to the present invention and demonstrate the relative improved effectiveness of same . in order to evaluate the prosthesis design according to the present invention , five pairs of adult human femurs were excised from imbalmed cadavers . all specimens were determined free of gross lesions and anatomical abnormality by visual inspection and x - ray . one femur from each pair was cleaned and a rosette type , electrical resistance strain gage was cemented to the medial surface of the calcar femorale . additionally uniaxial strain gages were cemented to each bone on the lateral surface just below the greater trochanter , on the medial surface below the level of the lesser trochanter , on the medial surface above the level where the prosthesis tip would reside , and on the medial surface distal to where the tip would reside . each selected femur , with instrumentation attached , was secured at its distal end in a holding jig , and was placed in a mechanical testing machine . compressive loads were applied in 50 pound increments up to 450 pounds to the head of the femur along a line passing through the center of the head and the center of the distal condyles . each bone was exposed to the loading regime six times . strains were noted at each gage location and readings used to calculate principal strains for the calcar location . particularly maximum axial ( compressive ) strains and maximum hoop ( tensile ) strains were determined which are a function of applied load . results are tabulated in table i . each of the five femurs from example 1 was appropriately drilled and a standard commercial austrian moore femoral component ( f . c .) prosthesis was implanted therein with bone cement following standard surgical procedure . each specimen was then retested according to the procedures set forth in example 1 , the gage readings recorded , and the strains calculated therefrom . results are tabulated in table i . the five femurs of example 2 ( with prosthesis implanted ) were modified by cutting a 3 mm slot in the cement and bone along the line of contact between the prosthesis collar and the osteotomy . all collar - calcar contact was thus effectively removed , simulating improper prosthesis implantation or conditions following resorption of calcar bone . the slot dimension of 3 mm was based on clinical observations that a majority of cases of subsidence of prostheses involve movement of 3 to 5 mm , and that movement of greater than 4 mm may be associated with chronic deep infection . after undermining the collar , the loading tests of example 1 were repeated with calculated strains being tabulated in table i . the moore prosthesis employed in example 2 was modified to generate simulated prostheses generally according to the teachings of the present invention . while it was not possible to exactly duplicate a prosthesis according to the present invention , the moore prosthesis was modified as follows : ( 1 ) a tapered or relieved area was machined on the medial surface of the stem buttress , and the relieved area filled in with rtv silastic rubber . ( see element 40 of fig1 ). ( 2 ) the anterior , posterior , lateral and medial surfaces of the stem below the collar were machined to remove taper in the stem grooves in the anterior and posterior surfaces were filled in with silver solder and machined smooth . all surfaces were then polished whereby the stem was rendered smooth and untapered throughout its length . the resulting cross sectional area of the stem was smaller than would occur with a commercial prosthesis incorporating the instant design . ( 3 ) an rtv silicon rubber tip was attached to the distal end of the prosthesis similar to that shown in fig5 . the opposite femur of each pair from which the femurs of example 1 were chosen were then tested in the same manner as set forth in examples 1 , 2 and 3 . in other words the opposite femurs were : ( c ) a 3 mm slot was cut beneath the prosthesis collar to undermine same , and the femur was tested . all strain results are tabulated in table i . table i__________________________________________________________________________principal strains in the surface of the femoral calcaraustin - moore prosthesis clemson prosthesis % % femur , case pcomp decrease ptens θ * r / l pmin decrease max θ__________________________________________________________________________2736 l intact - 771 67 2 . 7 r - 1237 100 - 1 . 6 prosthesis - 390 49 165 6 . 6 - 656 47 174 - 22 . 1 undermined - 37 95 251 - 6 . 6 - 460 63 227 - 30 . 22787 r intact - 874 178 - 8 . 8 l - 1580 127 12 . 6 prosthesis - 154 82 271 17 . 4 - 583 63 22 27 . 9 undermined - 161 82 364 23 . 1 **- 573 68 447 - 39 . 22790 r intact - 1078 282 - 2 . 5 l - 1486 - 13 10 . 4 prosthesis - 522 52 137 3 . 0 **- 229 84 282 17 . 1 undermined - 93 91 47 - 32 . 0 - 15 99 181 15 . 32795 l intact - 1306 185 4 . 4 r - 2875 347 - 5 . 3 prosthesis - 186 86 238 - 10 . 4 **- 2173 24 29 - 10 . 4 undermined - 10 99 281 - 18 . 7 - 669 77 - 14 - 13 . 32811 r intact - 895 326 - 3 . 9 l - 2495 419 0 . 4 prosthesis - 194 78 59 16 . 6 **- 2194 14 576 10 . 9 undermined - 58 94 54 28 . 6 - 340 86 379 26 . 3__________________________________________________________________________ * angle θ is the estimated angle of deviation . ** stem lubricated with silicone to ensure no shear load across stemcement interface . as can be seen from the results set forth in table i , a significant decrease in compressive strain is experienced in the femur when the moore prosthesis is implanted therein . such of course refers to the shielding of the calcar as noted hereinabove . moreover , when the collar of the moore prosthesis is undermined , virtually no compressive strain remains (- 10 to - 161 ). conversely , with three out of four of the modified prostheses according to the present design ( 2790l excluded ), significantly less percentage reduction in compressive strain on the femur was experienced . such indicates that the prosthesis of the present invention more closely approximates the strain experienced by the normal femur , even when the collar is undermined to simulate subsistence of the prosthesis . having described the present invention in detail , it is obvious that one skilled in the art will be able to make variations and modifications thereto without departing from the scope of the invention . accordingly , the scope of the present invention should be determined only by the claims appended hereto .
an improved hip prosthesis designed to simulate forces on a femur like those experienced by a normal , healthy femur . a ball is located atop the prosthesis at a proper anatomical angular relationship with a neck and collar therebelow . the prosthesis stem extends from the collar to a distal tip and includes a buttress section , a middle section and tip section . an inner surface of the buttress section is relieved and a compressible material is located thereat . the middle and tip sections of the stem are smooth , of common cross section , without any significant taper and the tip is adapted to avoid transmission of significant axial forces to the femur therebelow . when implanted with a luting agent , the majority of forces are axial compressive forces applied to the calcar and there is little or no wedging of the prosthesis in the medullary canal ; little or no shear forces across the prosthesis - luting agent interface ; and little or no axial stresses from the prosthesis tip distal to same .