GB2118441A - Articulating joint prostheses - Google Patents

Abstract

An intramedullary prosthesis, particularly a hip prosthesis, comprises an articulating member (12) at one end and a stem (18) at the other. The stem is shaped to conform substantially to the transverse sections of the medullary canal socket into which it is to be inserted. The stem is preferably covered with a porous resilient coating (26) which becomes compressed as the stem is inserted into the socket. <IMAGE>

Description

SPECIFICATION Articulating joint prosthese#s This invention relates in general to orthopedic implantation of articulating joint prostheses of the type known as intramedullary prostheses or endoprostheses, such as intramedullary hip prostheses.

For many years surgeons have been able to replace the ball of the hip joint with a metal ball. This was done by removing the patient's ball and a part of the neck from the upper end of the femoral bone. A metal prosthesis implant, having a ball, neck, and stem, was then inserted into the medullary canal of the femur.

Prior to such insertion, the more centrally-positioned,softer, cancellous bone of the medullary canal had been rasped to form a bone cavity, or stem socket, to accept therein the stem of the prosthesis.

The rasps used to form the stem socket were variable in shape and were not precisely correlated with the shape of the desired prosthesis. Transverse sectional dimensions of the stem, at most points along the length thereof, were substantially smaller than the corresponding sectional dimensions of the prepared stem socket. Hence, the stems were generally loosely received within their sockets. Many patients who received such a prosthesis were substantially impaired in their ability to move due to excessive pain and/or to the limited range of articulation of the joint which received the prosthesis.

To better stabilize such stems, they were first provided with transverse holes, and many years later they were provided with pores on their outer surfaces. Bone was expected to grow into the holes and/or pores of the stems. It was hoped that tissue ingrowth would improve the stability of the stems with respect to their sockets.

Because the shapes of the stems with pores were patterned after the shapes of the stems with holes, transverse sectional dimensions of the stems with pores were also, at many points along their length, appreciably undersized with respect to the corresponding sectional dimensions of their stem sockets. It was felt that such stem undersizing was necessary in order not to fracture the femoral bone during insertion of the stem into the prepared stem socket. Because of such deliberate stem shape undersizing, the known stems lacked the necessary stability when inserted into their sockets and, therefore, could not properly transfer loads to the bone surrounding the stems.

Certain types of articulating joints sustain, in use, high mechanical loads, e.g., hip joints, where stresses occur in the bone which surrounds and defines the medullary canal. Due to poor stem fixations within the medullary canals, many patients who received such undersized stems experienced limited motion due to pain.

Efforts to obtain improved stabilization for such undersized stems lead to the injection of a bone cement paste into the prepared stem socket. The cement cures within the fills the void space between the external surface of the undersized stem and the adjacent tissue. Bone cement became widely used and is not generally accepted as means for fixing a stem within its socket.

Bone cement typically includes an acrylic polymer powder which is premixed with a compatible liquid acrylic monomer system to produce a doughy paste. The stem is rapidly inserted into the cement paste which then cures or polymerizes into hard cement between the stem and the bone. The hard cement is expected to anchor the stem within the stem socket.Using cement, variations in implantation procedure could be made, such as: a. changing the manner in which the cement was injected into the prepared stem socket; b. reducing the viscosity of the cement in order to improve the inter-locking between the cement liner and the porous cancellous bone; c. lengthening the stem; d. increasing the medial to lateral dimensions of the stem; and e. eliminating the flange at the prosthesis neck so that only a small portion of the stem's medial#and/or lateral outer surfaces at any given longitudinal elevation would impinge against adjacent dense cortical bone during manual insertion of the prosthesis.However, the dimensions of the remaining transverse sections of the stem along its length, above and below such elevation, were still made substantially smaller than the corresponding dimensions of the transverse sections of the stem socket. This stem undersizing promoted ease of stem insertion and prevented fracture of the dense femoral cortical bone.

It will be appreciated that cement paste allows a surgeon only a very short time interval, typically 5 minutes, within which to fixate the stem within its socket. Subsequently, as the cement polymerizes and hardens, it may shrink leading to the creation of tiny gaps or voids between the cement and the stem on one hand, or/or the cement and adjoining tissue on the other hand. Such voids have been known to adversely affect the ability of the cured hard cement to uniformly transfer load stresses between the stem and the surrounding bone.

But, when the cement non-uniformly transfers such load stresses, there can result a loss of bone starting from the upper end of the femur and leading to a gradual degradation of the useful life of the implanted prosthesis. In addition, the hard cement itself can be expected to fracture, even as early as 3 to 5 years after surgery. In some extreme cases, cement failure also leads to structural stem fracture. When the cement and/or the stem fractures, the patient suffers great pain, disablement, and requires a new implantation.

A re-implantation of a new prosthesis requires that the old prosthesis be forcefully removed, the hard cement drilled out, and the medullary canal re-reamed, all of which may lead to trauma and dangerous slide effects in the patient's body.

Also, the possible migration of unreacted monomer from the bone cement to tissue, and the need for the bone cement to undergo an exothermic polymerization may result in serious damage to tissue surrounding the prosthesis. Such damaged tissue leads to a loosening of the stem within its socket.

Attempts to develop a cementless stem fixation involved using pores on the stem surface, aforementioned, or adding around the stem a porous outer coating consisting of a ceramic, polymeric, or of a composite of polymer, glass, and/or ceramic. The coated stem was inserted into the stem socket without cement, see for example U.S. patents 3,938,198, 3,986,212,4,164,794 and 4,307,472.

One known type of porous composite coating, which has the ability to encourage tissue to grow into its pores, is described in "Porous Implant Systems for Prosthesis Stabilization" by C. A. Homsy, et al, Reprint from Clinical Orthopaedics, Nos. 89 Nov.-Dec., 1972, pp. 220-235, and in U.S. patent 3,992,725 and foreign patents corresponding thereto. This known coating was bonded to the stems of conventionally-shaped and sized prostheses.

The use of conventionally-shaped prostheses was responsible for many clinical failures. It was discovered that the void space in the stem socket was surrounded substantially be relatively soft cancellous bone which could not sustain the mechanical stress loads imposed thereon. Therefore, the advantages of this known composite coating were not fully utilized until the advent of the present invention.

The sucess of any implant is typically measured by its ability to assume and carry out the natural functions of the joint in which it is implanted. Thus, an implant must be capable of sustaining the required compressive and flexural stresses imparted to it during normal joint movements.

Prior to this invention, known medullary prostheses, especially hip joint prostheses, frequently failed to accommodate normal body functions primarily because the significance and criticality of the transverse sectional dimensions of the stem were not fully appreciated.

In contrast, the present invention recognises for the first time the importance of the cross section of the stem of an intramedullary prosthesis in achieving adequate stem fixation and uniform stress distribution.

In particular, the present invention is based on the recognition of the importance and criticality of the stem's transverse sectional dimensions, along the entire length thereof, relative to the corresponding transverse sectional dimensions of the medullary canal, as defined by the surrounding dense, cortical bone, known as cortex, in achieving: (1) an adequate initial stabilization within the stem socket, (2) an enduring subsequent stem stabilization, (3) a distributed longitudinal load transfer, (4) an improved load transfer between the stem and surrounding hard cancellous bone and cortical bone, and (5) reduced localized stress zones in the bone opposite to and facing the entire stem.

Accordingly, the invention provides an improved intramedullary prosthesis comprising a head portion having a ball formed thereon and a stem portion extending from the head portion for insertion into the medullary canal of the bone into which the prosthesis is to be inserted wherein the stem is shaped along its length to conform substantially with the cross-section of the medullary canal as defined by the cortical bone or cortex and into which it is to be inserted, at all points along the length thereof.

In a more specific and preferred aspect, the invention provides an intramedullary prosthesis comprising a head portion having a ball-shaped member thereon, and a stem portion extending from said head portion said stem portion being shaped so that is corresponds substantially to the cortical geometry of the medullary canal in which it is to be inserted and being covered with a thin layer of resilient porous material whose thickness is such that the cross-sectional dimension of the coated stem at any given point is slightly longer than the corresponding dimension of the medullary canal at that point, whereby, when the stem is inserted into the medullary canal, the resilient, porous surface layer is compressed between the stem and the cortical bone surrounding the medullary canal but without substantially restricting the porosity of said layer, thereby to permit the subsequent ingrowth of tissue into said porous layer.

In this preferred embodiment, the compression fit initially instantly stabilizes the stem within its socket, and subsequently allows tissue to grow into the coating's pores. The initial compression fit and subsequent tissue ingrowth both tend to ensure the stem's long term stability and the stem's load transfer capabilities.

In the preferred embodiment, the stem itself, which will usually be of metal, will most preferably have transverse sectional dimensions along its entire length which are slightly undersized relative to the transverse sectional dimensions of the prepared stem socket, the thickness of the resilient coating being such that the overall dimensions of the coated stem exceed the corresponding dimensions of the prepared socket by an amount ranging from 0.2% to 7%.

By shaping the stem part of the prosthesis to conform substantially to the geometrical shape of the medullary canal defined by the dense cortical bond, and by bonding to the stem a compressible, porous, resilient coating, it is now possible to obtain, at implatation, a generally uniform press fit between the stem coating and the surrounding hard cancellous bone and cortical bone. Such press fit allows the stem to distribute mechanical loads to the cortical bone, especially in the diaphyseal region, and to the relatively hard cancellous bone and to the cortical bone in the metalphyseal and epiphyseal regions. In addition, the compressed coating also acts as a shock absorber, thereby further improving the long-lasting, postoperative results of the implantation.

When implanting the prosthesis of the present invention the medullary canal of the bore into which the implant is to be made is reamed and rasped to form a stem socket having a predetermined shape and length to receive therein either the preferred oversized and coated stem in which case no cement is used or a slightly undersized uncoated stem, still shaped in accordance with the requirements of this invention, but in this case together with a thin cement layer. Although the uncoated but shaped stems are less peferred, nevertheless even they show considerable advantages over the essentially unshaped stems of the prior art.

In the case of the coated stem, after preparing the socket, the stem is properly oriented at the mouth of the socket, and with adequate force the stem is gradually pushed into the socket, whereby the resilient, porous coating becoes slightly compressed. At the metaphyseal and epiphyseal levels of the medullary canal, the coating becomes uniformly compressed, whereas at the diaphyseal level of the canal, the medial and lateral surfaces of the coating become predominently compressed. These compressions, however, are such that the porosity of any portion of the coating is only slightly reduced. The bone tissue will then be in intimate contact with the pores of the compressed coating to allow rapid tissue ingrowth therein.

The invention is further described with reference to the accompanying drawings wherein: Figure 1 is a side elevation view of a hip joint prosthesis according to the broad aspect of the present invention.

Figure 2 is a right side elevation of the prosthesis taken along line 2-2 in Figure 1 with the flange, neck, and ball removed.

Figure 3 is a sectional view of the stem, taken along line 3-3 in Figure 1, showing the flange.

Figure 4 is a sectional view of the stem taken along line 4-4 in Figure 1.

Figure 5 is a side elevation view of a prosthesis according to the preferred aspects of this invention, being a prosthesis substantially as shown in Figure 1, but with a resilient, porous, tissue-promoting coating thereon.

Figure 6 is an elevation view of the hip joint prosthesis of Figure 5 installed in the upper end of a femur with its stem fully extending into the femur's medullary canal.

With particular reference to the drawings, the prosthesis of this invention, generally designated as 10, has a stem 18 adapted for insertion into the medullary canal 28 (Figure 6) of a femur 27. Prosthesis 10 is illustrated as being a hip joint prosthesis or femoral ball prosthesis. However, the portion of the description relating to stem 18 and the stem's interrelation with and its fixation within the medullary canal 28 would be equally applicable to other articulating joint prostheses.

With particular reference to Figures 1-4, prosthesis 10 includes a ball 12, a flange 16, and a neck 14 which extends therebetween. A stem 18 comprises a shank portion which extends away from the opposite side of flange 16 substantially at a right angle thereto. In side elevation, as shown in Figure 1, stem 18 is curved at its proximate end and tapers down at its distal end to an annular flange 20.

Flange 20 is shown as having a circular transverse section and extends radially outwardly by slightly less than 2 millimeters beyond the main body of stem 18. The proximate end of stem 18 is relatively flat and has an inner surface 22 which is rounded and an outer surface 24 which is flat but with rounded edges, as shown in Figures 3-4. Instead of haing a circular section, flange 20 can have an oval section.

It should be understood that the improved stem 18 should be made in at least three distinct shapes, each shape having a set of distinct dimensions designated in Figures 1,3 and 4 by letters a through g. It has been found in practice that three distinct shapes for a femoral prosthesis will accommodate most shapes of femurs 27 normally encountered in human skeletons. Accordingly, such three distinct shapes for implant 10 can be manufactured in advance and made available to the surgeons, together with instructions for preparing corresponding stem sockets, as will be subsequently described.

The following are dimensions in millimeters for one such shape for a typical small stem prosthesis: a = 139.7 mm e = 10.0 mm b= 8.2 mm f = 32.0 mm c= 8.1 mm g= 8.0mm d= 12.0mm In a preferred embodiment, as shown in Figures 5-6, a coating 26 of a resilient, porous, tissue-ingrowthpromoting material is bonded to and around stem 18 and completely covers it. No coating is provided around flange 20.

It is preferred that the transverse sections of stem 18 should constitute at least seventy percent (70%) of the corresponding transverse sections of the medullary canal 28 defined by the endosteal or inner contour of dense, hard cortical bone for metaphyseal and epiphyseal segments of a typical long bone of the skeleton, and at least ninety percent (90%) of the corresponding transverse sections of the diaphyseal segment.

Any resilient, tissue-ingrowth-promoting, porous coating 26 may be utilized, so long as it is compatible with the body system of the patient and will bond adequately to the stem's base material which is typically a metal, such as an ASTM F-75 chromium-cobalt-molybdenum orthopedic alloy.

A preferred such coating composition is described in said U.S. Pat. No. 3,992,725, and is sold by Vitek, Inc., Houston, Texas, U.S.A., under the registered trademark PROPLAST.

Briefly, this material, at least in its preferred form, comprises a resilient, fibrous porous structure composed of carbon or graphite fibres, optionally in admixture with a proportion of polytetrafluoroethylene fibres, bonded together with a sintered polytetrafluoroethylene resin.

The porous coating should be bonded at least to substantially the entire surface of the prosthesis that is normally designed for fixation. For example, the stem of a femoral prosthesis would be entirely coated.

It is preferred that coating 26 have a thickness of about 2 millimeters, which is a compromise between several factors including: desired stem strength, coating compression, tissue ingrowth into the coating, and size of the patient's medullary canal. Greater coating compression will lead to a larger porosity reduction.

Before implantation, a stem socket 25 must be prepared in the femur 27. The sectional dimensions of the void space in socket 25 are made such as to obtain at least a one percent and preferably approximately ten percent compression of coating 26, after stem 18 is pushed down to its final seated position in socket 25, as shown in Figure 6.

Coating 26 is sufficiently porous and sufficiently resilient so that when it becomes partially compressed during the forceful insertion of stem 18 into the preformed stem socket 25, the coating's porosity characteristics and tissue ingrowth capabilities will only be slightly impaired. Coating 26 will also be able to accommodate non-uniformities at least in the upper portion of socket 25, and still achieve a substantially uniform compression fit or interference fit with the abutting hard bone, mostly cortex.

A proper preparation of socket 25 will take full advantage of the shape of prosthesis 10. For example, outer surface 24 is not covered by flange 16 and extends substantially perpendicularly away from flange 16.

Surface 24 curves sharply and then extends in a substantially straight line to bottom flange 20.

With such a geometrical configuration for prosthesis 10, when the lower end of stem 18 is selected to fit within the prepared socket 25, then coating 26 will be compressed by surrounding bone along substantially the entire length of stem 18.

A combination of specific surgical tools will be used by the surgeon to properly prepare socket 25 for receiving one of the three shapes for the femoral prosthesis 10 provided to the surgeon, as above described.

In general, socket 25 is reamed and rasped into proper shape to allow the oversized coated stem 18 to become inserted therein by the use of force applied to implant 10. As a result, the tissue around the socket's void space will totally surround and make intimate pressure contact with the stem's coating 26 substantially along its entire length.

In particular, with a suitable radiograph, the proper prosthesis shape can be predicted. The instruments subsequently used to develop socket 25 will verify whether the proper shape for prosthesis 10 was predicted with the radiograph.

Standard surgical approaches should be used to expose the patient's hip joint. The approach selected should allow access to the proximal femur along its longitudinal axis. When the hip joint is exposed, dislocation of the femoral head from the acetabulum may be accomplished either with or without a trochanteric osteotomy.

In the following description trochanteric osteotomy is performed along the plane Y-Y shown in Figure 6, and the trochanter is pivoted away from the neck and ball of the femur.

Using a guide unit, the osteotomy of the femoral neck is performed. The medial level of the osteotomy should be as high as possible above the superior border of the lesser trochanter.

A rongeur is used at the apex of the two osteotomies to develop an entrance cavity for a hand reamer approximately 8 mm in diameter. If the trochanter has not been released, a small drill bit is used to develop the entrance cavity for the hand reamer. The reamer is directed along the long axis of the femur 27 to gain access to the medullary canal 28 through the metaphyseal bone. A guide should be used to direct the location of the tip of the hand reamer or drill bit.

Thereafter, a guide rod of a powered flexible reamer is placed down the longitudinal axis of femur 27 following the cavity developed by the hand reamer or drill bit.

The flexible reamer is used in 0.5 mm size increments to develop the distal end of socket 25 in the diaphyseal segment of the medullary canal. The guide rod previously placed in the canal also acts as a guide for the cannulated cutting heads of the reamer. The reamer cutting heads are increased in size until endosteal cortical bone is touched in the diaphyseal portion of the medullary canal. The size of this reamer indicates and fixes the size of the final reamer used for preparing socket ?5 substantially along the longitudinal axis of femur 27. This final reamer size corresponds to a particular prefabricated shape for implant 10, for example, a small prosthesis 10 having the dimensions a-g shown in Figures 1,3 and 4.

As previously mentioned, implant 10 is made in three distinct shapes in order to accommodate most shapes of femurs normally encountered in making femoral implantations.

Using translational motion in line with the longitudinal axis of the femur, manual rasping of the developed stem socket with an appropriately sized rasp is carried out. When stem socket 25 is properly sized and shaped, stem 18 is then pushed down into the socket. Because coated stem 18 is oversized by an amount ranging from 0.2% to 7% in its transverse sections as compared to the corresponding transverse sections of its prepared socket 25, it cannot be forced down manually and must be driven in gently with a surgical mallet. Flange 20 serves to protect the leading edge of the coating 26 against abrasion during the forced insertion of coated stem 18 into its socket 25.

Utilizing the foregoing steps, the improved prosthesis 10 of the present invention is implanted with consistent positive results predicated on the implant achieving instant stability in its socket 25. Tissue will start rapidly to grow into the porous coating 26 to ensure proper long-term fixation of the prosthesis.

The soft porous coating 26 will make intimate physical contact with the surrounding bone and prevent abrasion of the cortical bone or of the hard cancellous bone during physical movements of the body subsequent to implantation. Moreover, by virture of the resiliency of coating 26, a shock gradient is established across the coating that assists in distributing the compressive loads along the implanted stem 18, leading to a longer lasting and more comfortable implant for the patient.

Patients who have received such implants 10 have generally been able to bear with comfort normal weight as early as 3 to 6 weeks after surgery.

Although much less desirable, a similar technique can be employed for the implantation of a prosthesis 10 shaped according to the invention, but not having a resilient, porous, tissue-ingrowth-promoting coating on the base material of stem 18.

The uncoated stem 18 will have to be implanted by the use of a bone cement to form a cement liner around stem 18. The improved load transfer to the cement liner and the support provided to said liner by hard cancellous bone and by hard cortical bone will mediate against premature failure of the cement.

For an uncoated stem 18, bottom flange 20 is either deleted or its outer surface is grooved vertically so that the cement can surround the end of the stem during implantation. The grooved flange 20 would be additionally helpful in centralizing the stem vis-a-vis its surrounding cement liner.

A plug of cement or of plastic is usually positioned distal to the end of the stem to maintain back pressure in the cement during prosthesis emplacement.

As stated above, whilst the improved prosthesis 10 of the present invention is illustrated and described with respect to a hip joint prosthesis, it will have applications to other articulating joint prostheses, wherein the load transmitted through the joint is conveyed by the implant to the body skeleton by means of a stem or an extension which has to fit within a prepared cavity or socket in the medullary canal portion of the skeletal element in the patient's body.

Claims (12)

1. An intramedullary prosthesis having a stem part for insertion into a stem socket formed within the medullary canal of a patient's bone, as defined by the cortex of a patient's bone, characterized in that said stem part has, over substantially the whole of its length, transverse sectional dimensions which substantially approximate the geometry of said medullary canal.

2. A prosthesis according to claim 1, characterized in that said stem part has a base whose transverse sectional dimensions substantially along its entire length are slightly undersized relative to the transverse sectional dimensions of said stem socket.

3. A prosthesis according to claim 2, characterized in that a thin, resilient, tissue-ingrowth-promoting porous coating material covers substantially the entire outer surface of said base, whereby the transverse sectional dimensions of the coated stem portion are slightly oversized in relation to the corresponding transverse sectional dimensions of said stem.

4. A prosthesis according to claim 3, wherein said coating has a thickness approximating two millimeters.

5. A prosthesis according to claim 3 or 4, wherein the resiliency of said coating is such that when said stem part is inserted into its stem socket, said coating becomes compressed by an amount ranging from one percent (1%) to ten percent (10%) of its original thickness.

6. A prosthesis according to claim 3,4 or 5, characterized in that said porous coating material comprises a resilient porous structure of carbon or graphite fibres, optionally in admixture with a proportion of polytetrafluoroethylene fibres, and bonded with a sintered polytetrafluoroethylene resin.

7. A prosthesis according to any one of claims 3-6, characterized in that said coated stem is oversized in its transverse sectional dimensions with respect to the corresponding sectional dimensions of said socket by an amount in the range 0.2% to 7%.

8. A prosthesis according to any one of claims 2-7, characterized in that the transverse section of said stem base constitutes at least seventy percent (70%) of the transverse section of said medullary canal, for the metaphyseal and epiphyseal segments of said bone, and at least ninety percent (90%) of the transverse section of said medullary canal for the diaphyseal segment of said bone.

9. A prosthesis according to any one of the preceding claims, characterized in that said prosthesis comprises a head portion having a flange, a neck extending from one side of said flange, and a ball on the end of the neck; and said stem part having a proximal end extending from the opposite side of said flange substantially at 900 thereto, and a distal end extending from said proximal end at an angle approximating the angle of said socket into which said stem part is to be inserted up to its neck and ball.

10. A prosthesis according to claim 9, characterized in that the tip of said distal end of said stem has a curved flange extending radially outwardly and having its largest dimension slightly less than the corresponding dimension of said stem socket at the elevation of said curved flange.

11. A prosthesis, substantially as hereinbefore described with reference to Figure 1 of the accompanying drawings.

12. A prosthesis, substantially as hereinbefore described with reference to Figures 5 and 6 of the accompanying drawings. ~~~~~~~~~~~~~~~~~~~~~~~~~~~~~~~