WO2012126496A1

WO2012126496A1 - A tibial tray for a knee joint prosthesis and a knee joint prosthesis including same

Info

Publication number: WO2012126496A1
Application number: PCT/EP2011/054139
Authority: WO
Inventors: Patrick HOCHULI
Original assignee: Smith & Nephew Orthopaedics Ag
Priority date: 2011-03-18
Filing date: 2011-03-18
Publication date: 2012-09-27
Also published as: EP2685936A1; EP2685936B1

Abstract

A tibial tray (1) for a knee joint prosthesis comprises a platform (4) including a proximal bearing surface (5) and a distal fixation surface (6). A keel (9) projects from the distal fixation surface (6). The keel (9) is located centrally of the tibial tray (1) in a medial-lateral direction and is substantially planar in a sagittal place with a distal edge (10) that extends obliquely with respect to the proximal bearing surface (5) of the platform (4). Preferably, the keel (9) is substantially triangular is shape and has its deepest part towards the posterior aspect of the tray (1). A knee joint prosthesis including the tibial tray (1) is also provided. Preferably, this prosthesis comprises a unicondylar prosthetic device with a femoral component (2) adapted for attachment to a femur and a floating insert (3) adapted to fit between the femoral component (2) and the tibial tray (1) when the prosthesis is implanted in a patient.

Description

A TIBIAL TRAY FOR A KNEE JOINT PROSTHESIS

AND A KNEE JOINT PROSTHESIS INCLUDING SAME

The present invention relates to a tibial tray for a knee joint prosthesis and to a knee joint piOsdiesis including such a tibial tray.

Many varying prosthetic devices are available for knee joint replacement. These include bicondylar prosdiedc devices, where bodi condyles of d e knee are replaced, and unicondylar prosdiedc devices wherein only of the knee condyles is replaced. In such a procedure, dbial components are used to replace either or both of the medial and lateral condyles of the patient. A single, total femoral component or two partial femoral components may then be used to cooperate with the tibial component or components. However, unicondylar prosdieses have to be precisely installed otherwise they are prone to failure. The Oxford unicondylar knee system was introduced to overcome this problem. In this system, a floating insert is located between a tibial component in the form of a tibial tray and d e femoral component so that die insert can move with respect to both the tibial tray and die femoral component. This reduces the degree of precision required to produce a satisfactory knee joint but it is still necessary for the tibial and femoral components to be installed carefully.

One aim of the present invention is to provide a tibial tray for use in such a unicondylar prosthetic device tiiat facilitates its positioning during surgery in die tibia of a patient and that therefore increases die degree of precision that can be achieved during its installation.

A furdier aim is to provide a knee joint prosthesis including the aforementioned tibial tray tiiat includes a floating insert adapted for use with the tibial tray.

According to a first aspect of the present invention tiiere is provided a tibial tray for a knee joint prosthesis comprising a platform including a proximal bearing surface and a distal fixation surface; and a keel tiiat projects from the distal fixation surface and that extends in an anterior-posterior direction with respect to the position of the tray when in use; characterised in that the keel is located centrally of the tibial tray in a medial lateral direction and is substantially planar in a sagittal place widi a distal edge d at extends obliquely witii respect to die proximal bearing surface of d e platform.

Preferably, die keel has its deepest part towards die posterior aspect of the tray.

Preferably also, the keel is substandally triangular is shape. Advantageously, an apex of die triangular keel is between 6 mm and 11mm from die distal fixation surface.

Preferably also, an angle between the distal edge of die keel and die proximal bearing surface is between 10° and 30° inclusive and is preferably approximately 17°.

Preferably also, die keel extends in a sagittal plane over half the lengd of d e anterior- posterior length of die tray.

Prefeiably also, die proximal bearing surface is smoodi and generally planar.

Preferably also, the distal fixation surface of the platform is configured for attachment to a dbia by a bone cement.

Preferably also, die distal fixation surface of die platform is provided with one or a plurality of cement pockets. Advantageously, each of die cement pockets is aligned in an anterior-posterior direction.

Preferably also, the distal fixation surface of the platform is roughened.

Preferably also, d e platform defines a wall that projects in a proximal direction at an intercondylar edge of the proximal bearing surface. Advantageously, d e wall extends proximally, in use, in a sagittal plane.

According to a second aspect of the present invention diere is provided a knee joint pros diesis comprising a tibial tray according to the first aspect of die present invention. Preferably, tl e knee joint prosthesis additionally comprises a femoral component adapted for attachment to a femur, and a floating insert adapted to fit between tlie femoral component and the tibial tray when die prosthesis is implanted in a patient, the insert having a femoral side shaped to interface slidingly widi an outer surface of die femoral component during flexion of the knee and a tibial side shaped to interface slidingly widi the proximal bearing surface of die tibial tray.

Preferably also, the insert is not symmetric about a sagittal plane. Advantageously, tlie insert has an intercondylar side that is longer in lengtli d an an opposite superficial side.

Preferably also, a corner at a posterior end of d e intercondylar side of the insert is extended to project rearwardly.

Preferably also, an angle between die intercondylar side and a posterior side of die insert is less dian 90°.

Preferably also, corners between die superficial side of d e insert and its posterior and anterior sides are ounded.

Preferably also, a surface of die dbial side of the insert is smoodi and generally planar.

Preferably also, an anterior-posterior profile of the insert is substantially wedge-shaped with the anterior height greater dian die posterior height.

Preferably also, in die sagittal plane die difference in height between a deepest point of die femoral side of the insert and a posterior edge of die femoral side of the inseit is no greater than 3 mm and is preferably of the order of 2mm.

Preferably also, in the sagittal plane die difference in height between a deepest point of the femoral side of die insert and an anterior edge of the femoral side of the insert is between 2mm and 6 mm inclusive and is preferably of the order of 4 mm. Preferably also, said outer surface of the femoral component defines two regions for flexion rotation in a sagittal plane of which a first region has a first radius of curvature and a second region has a second radius of curvature, die first radius of curvature being larger d an die second radius of curvature, and in d at the surface of die femoral side of tlie insert has substantially die same radius of curvature in die sagittal plane as die first radius of curvature of the femoral component.

Preferably also, said outer surface of die femoral component has a diird radius of curvature for varus/valgus rotadon in a coronal plane, and in diat the surface of die femoral side of die insert has substantially die same radius of curvature in d e coronal plane as die third radius of curvature of the femoral component.

Preferably also, die knee joint prosthesis comprises a unicondylar prostiiedc device.

The various aspects of die present invention will now be described by way of example with reference to the accompanying drawings, in which:-

Fig. l is a side view of a knee joint prosthesis including a tibial tray, a femoral component and a floating insert;

Figs. 2 to 4 are respective!₎' top, bottom anterior elevations of an embodiment of tibial tray forming part of die prostiiesis similar to that shown in Fig. 1 and in accordance with the present invention;

Fig. 5 is a cross-section along die line V-V in Fig. 4;

Fig. 6 is a cross-section along the line VI- VI in Fig. 3;

Figs. 7 and 8 are perspective views of the tray from above and below respectively. is a perspective view of a floating insert forming part of the knee joint prosthesis shown in Fig. 1;

Figs. 10 and 11 are respectively plan and anterior views of the insert shown in

Fig. 9;

Fig. 12 is a cross-section along the line XII-XII in Fig. 10;

Fig. 13 is a cross-section along die line ΧΙΙΙ-ΧΙΙΪ in Fig. 0;

Figs 14 and 15 ate side views of die knee joint prosdiesis similar to that shown in Fig. 1 showing die position of die floating insert relative to die tibial tray and the femoral component when die femoral component is positioned at 8° hyper-extension and at 125° flexion respectively;

Figs. 16 to 18 are side views of d e knee joint prosthesis similar to that shown in Fig. 1 but widi die floating insert shown in cross-section along a sagittal place and with a femoral component of the prosdiesis positioned at 0°, 30° and 80° of flexion respectively; and

Fig. 19 is a cross-section along die line ΓΧΧ-ΙΧΧ of Fig. 17.

A unicondylar knee joint prosthesis such as is shown in Fig. 1 comprises a tibial tray 1 , a femoral component 2 and a floating insert 3. The advantage of such prosdieses is diat tiiey can be implanted with minimal invasive surgical procedures and involve a small amount of bone resection. Bod the tibial tray 1 and the femoral component 2 are preferably made of a material that provides a smoodi sliding surface, is sufficiendy rigid and durable, and will not cause adverse patient reactions, for example a cobalt chromium mol_j'bdenum alloy or oxidized zirconium. In contrast, the floating insert 3 is preferably made of a material that can provide a good sliding interface with bodi the tibial tray 1 and the femoral component 2 and diat also provides good friction and wear characteristics. An example of a suitable material for the insert 3 is ultra high molecular weight polyethylene, a ceramic, oxidized zirconium or a combination of these. The tibial tray 1 and the femoral component 2 are bodi designed to be cemented in position. Conventional bone cements, such as those based on polymetiiylmethaciylate can be used.

An embodiment of die tibial tray 1 for use in such a prosthesis is shown in Figs. 2 to 8. It should be appreciated diat die embodiment of tray 1 shown in Figs. 1 and 14 to 19 of die drawings is shaped for implantation in die lateral side of a left knee or die medial side of a righ knee of a patient. A tray suitable for implantation in die medial side of a left knee or the lateral side of a right knee of a patient would be a mirror image of tiiis tray and is as shown in Figs. 2 to 8 of die drawings.

The tibial tray 1 comprises a platform 4 with a proximal bearing surface 5 and a distal fixation surface 6. The platform 4 is typically 2mm diick but may be between 1.5 mm and 3 mm diick dependent on die overall size of the tray and any particular patient requirements. The proximal beating surface 5 is smooth and generally planar. At die intercondylar edge of die platform 4 is a projecting wall 7 diat is linear and diat in use extends in a sagittal plane from the proximal bearing surface 5 and projects in a proximal direction. The wall 7 is provided to prevent dislocation of die insert 3 during use and to prevent abrasion of d e insert 3 by adjacent bone. In contrast, die superficial, anterior and posterior edges 5 of d e platform 2 form a continuous, asymmetric curve which approximates to the exterior profile of the underlying bone so that diere is minimal impairment of d e function of die cruciate ligaments and leg muscles when the implant is in use.

The distal fixation surface 6 is configured for attachment to a tibia and is preferably roughened, for example by sand-blasting to provide a key for cementation or by vacuum plasma spray (VPS), for example, for a cementiess version of the implant. In addition, the distal fixation surface 6 is provided with one or a plurality of cement pockets 8 that are preferably less dian 1.0 mm deep and typically around 0. 5 mm deep. These pockets 8 are aligned parallel to one another and are preferably in an anterior- posterior direction as if diey extended in a medial-lateral direction, the platform 4 may be weakened too much, Although with a thicker platform 4, such an alignment is possible.

Projecting from die distal fixation surface 6 is a keel 9 diat extends in an anterior- posterior direcdon widi respect to the position of the tray 1 when in use. The keel 9 therefore extends in a direcdon parallel to the cement pockets 8 and is located approximately centrally of die dbial platform 4 in a medial-lateral direction. This is important as it increases die strengdi of the tray 1. The keel 9 is substantially planar in a sagittal plane and triangular in shape widi a distal edge 10 th t cxtetids obliquely from an apex 11 with respect to the proximal bearing surface 5 of the platform 4. Preferably, die apex 11, which is at die deepest part of die keel 9, has a depdi D that is between 3 mm and 15 mm from die distal fixation surface 6. Preferably also, d e angle between the distal edge 10 of die keel 9 and die proximal bearing surface 5 is between 10° and 30° inclusive and is preferably around 17° with a few degrees difference eiti er way. The deepest part of die keel 9 is also preferably towards die posterior aspect of die tray 1. Overall, die keel 9 extends in a sagittal plane along the greater part of die anterior- posterior lengdi of the platform 4 and therefore die tray 1. Typically, die anterior end of the distal edge 0 is approximately 6.2 mm from anterior edge of die platform 4 and the posterior end of die distal edge 10 is approximately 5.0 mm from die posterior edge of die platform 4. As die overall anterior-posterior lengdi of the platform 4 may be between approximately 38.0 mm and 55.4 mm dependent on die tibial plateau size of die patient it will be appreciated tiiat in all cases the keel 9 extends over half the length of d e tray 1. To ensure a strong bond between the tray 1 and die tibia, the central section of the keel 9 may be pierced by an aperture 12 to allow cement to flow tiirough it during implantation. The shape of the aperture 12 may mirror the triangular shape of the keel 11.

The keel 9 facilitates positioning and fixation of the tray 1 during implantation to a resected end of a tibia. The surgical medio d of implanting the tibial tray 1 involves resecting at least a portion of a condyle of a patient's tibia to create a surgically-prepared tibial surface. The surgeon may then form a slot in the surgically-prepared tibial surface diat extends posteriorly from an opening formed in an anterior surface of die tibia. When positioning die tibial tray 1, die keel 9 enables the tray 1 to be slid into place over tl e top of the prepared tibial surface from anterior to posterior into the tibial resection and enables the platform 4 of the tray 1 to be located with precision over tlie resected end of the tibia. Bone cement may be used to secure tlie tray 1 to tlie resected tibia and may be injected into tlie slot once tlie tray 1 has been correctly positioned.

As indicated above, tl e tibial tray 1 forms part of a unicondylar knee joint prosthesis as shown in Fig. 1. 'Hie femoral component 2 of this prosthesis has a curved smooth outer surface 13 that forms a sliding interface with tlie insert 3, as is described in more detail below. Opposed to tlie outer surface 13 is a fixation surface 14, which may be roughened, for example by sand-blasting or by vacuum plasma spray (VPS), from which two aligned pegs 15 project to enable the component 2 to be positioned and secured to a femur so that tl e component 2 is prevent from rotating relative to tlie femur.

As shown in Figs. 16 to 19, in the sagittal plane, die surface 13 of the femoral component 2 defines two regions 16 and 17 for flexion rotation in a sagittal plane of which the first, r region 16 has a first radius of curvature Rl and die second region 17 has a second radius of curvature R2. Tl e surface 17 with the second radius of curvature R2 defines tlie posterior part of tlie component 2 while die surface 16 with the first radius of curvature Rl defines the anterior part of the component 2 and imitates tl e distal shape of the femoral condyles. The first radius of curvature Rl is larger than tlie second radius of curvature R2 and typically tlie ratio of these two radii is between 1.3:1 and 1.8:1. The surface 13 of tlie femoral component 2 also has a diird radius of curvature R3 in a coronal plane for varus/valgus rotation, as shown in Fig. 1 . The radius of curvature R3 is substantially tlie same as the radius of curvature R2. This means that die surface of the posterior part of the component 2 is spheroidal whereas tlie surface of the distal or anterior part of the component 2 is toroidal.

The floating insert 3 is designed to slide between die proximal bearing surface 5 of the tibial tray 1 and die outer surface 3 of the femoral component 2. An embodiment of it will now be described in more detail witii reference to Figs. 9 to 13. The insert 3 has a concave femoral side 18 shaped to interface slidingl with tlie surface 13 of die femoral component 2 during flexion of die knee and a tibial side 19 shaped to interface slidingly with tlie proximal bearing surface 5 of die tibial tray 1, Tlie surface of the tibial side 19 of the insert 3 is dierefore smooth and generally planar like the proximal bearing surface 5 of the tibial tray 1. In addition, die anterior-posterior profile of die insert 3 is substantially wedge-shaped with die anterior height greater than the posterior height so tiiat it can be pushed into position between die tibial tray 1 and tl e femoral component 2. The difference in height between the lowest and highest parts of die concave femoral side 18 defines die resistance against luxation of the prosdiesis. However, in the sagittal plane the difference HI in height between the deepest point of die femoral side 18 and a posterior edge 20 of d e femoral side 18 should be no greater than around 3 mm and is preferably of the order of 2 mm otherwise too much force is required to push the insert 3 into position between the tibial tray 1 and die femoral component 2. Luxation towards die anterior is prevented by a difference in height H2 between die deepest point of the femoral side of the insert 18 and an anterior edge 21 of the femoral side 18 is between 2mm and 6 mm inclusive and is preferably of the order of 4 mm.

The concave nature of the femoral side 18 of tlie insert 3 is such tiiat its surface has substantially the same radius of curvature in the sagittal plane as the first radius of curvature Rl of anterior part of the femoral component 2. This means diat there is maximum congruency between the insert 3 and die femoral component 2 in extension. In addition, this surface in die coronal plane has substantially tlie same radius of curvature as die third radius of curvature R3 of the femoral component 2. This allows varus/valgus rotation of the knee in a coronal plane of up to 8°.

Ald ough it is possible for the insert 3 to be symmetric about a sagittal plane, preferably it is asymmetric as shown in Figs. 9 to 13. It should be noted in this regard that the embodiment shown in Figs. 9 to 13 is shaped for implantation in die medial side of a left knee or the lateral side of a right knee of a patient and therefore for use with a tibial tray 1 as shown in Figs. 2 to 8. An insert suitable for implantation in tlie lateral side of a left knee or die medial side of a right knee of a patient would be a mirror image of the insert 3 illustrated in diese drawings. As shown, overall tlie insert 3 is not symmetric about its sagittal plane although tlie surface defined by the femoral side 18 is symmetric about this plane and is approximately rectangular but with rounded corners. Beneath this femoral surface, the insert 3 is shaped to prevent excess rotation relative to tlie tibial tray 1 from taking place during use and to protect surrounding soft tissues from damage. It has an intercondylar side 22 that extends linearly and that is adapted for location adjacent the wall 7 of tl e tibial tray 1. This side 22 is longer in length than an opposite superficial side 23 of tl e insert 3, which has a rounded profile. Contact between tlie longer intercondylar side 22 of the insert 3 and the wall 7 limits extensive rotation of tlie insert 3 relative to tl e tibial tray 1 as the knee joint is moved. In particular, tlie coiner 24 at the posterior end of d e intercondylar side 22 may be extended and project rearwardly as shown in Fig. 10 for die express purpose of preventing extensive rotation relating to the tibial tray 1. The angle Al between the intercondylar side 22 and tlie posterior side of insert 3 is therefore less than 90° and is typically around 80°. The corner Λ2 between tlie intercondylar side 22 and the anterior side of the insert is equal to or less than 90° although the actual apexes of both corners are rounded. However, tlie corners between tlie superficial side 15 of the insert and its posterior and anterior sides are rounded in order to protects the surrounding soft tissue from damage during deep flexion and during hyperextension of the knee.

Tlie generally planar nature of tlie proximal bearing surface 5 of the tibial tray 1 means tiiat it is not able to guide motion between the femur and tlie tibia of tlie patient during movement of tlie knee joint. Tliis has to be controlled by tlie patient's own muscles, die capsule and tlie ligaments around tlie knee joint. It is dierefore important that the prosthesis is implanted with precision in a manner which causes minimum damage to tl e soft tissues around the knee. The prosthesis is designed to allow a range of motion between 8° hyper-extension to 125° flexion. These two positions are shown in Figs. 14 and 15 respectively. In hyper-extension, when die tibia is angled forwardly from die knee joint, die insert 3 sits approximately centrally in an anterior-posterior direction on tl e tibial tray 1, as shown in Fig. 14. However, during flexion, the femoral component 1 bears on die insert 3 and slides it along the proximal bearing surface 5 towards the posterior of die tray 1. At approximately 125° of flexion, which is typically maximum flexion, the posterior edge 20 and side of the insert 3 is very close to tlie posterior edge of the proximal bearing surface 5 of tlie tray 1, as shown in Fig. 15.

Flexion beyond 125° depends on tlie way any bony overhang on tlie posterior femoral condyle is treated. Such an overhang occurs mainly when tlie sizing or placement of tlie implant is not accurate and preferably any overhang is removed by a chipping it off with a curved chisel to prevent impingement between die femur and the insert 3 at greater than 125° of flexion.

During flexion, congruence between the insert 3 and tlie tibial tray 1 is presumed as tl e proximal bearing surface 5 and the tibial side 19 of tl e insert 3 are both generally planar. However, the contact condition between the surface 13 of tl e femoral component 2 and the femoral side 18 of the insert 3 varies with tlie degree of flexion. In full extension at 0° of flexion, as shown in Fig. 16, tl e sagittal and frontal radii are die same so that the surfaces 13 and 18 are totally congruent. This situation is maintained until approximately 30° of flexion when die region 17 with die smaller posterior radius R2 of die surface component 2 comes into contact with the surface 18, as shown in Fig. 17. Between approximately 30° and 80° of flexion, the latter of which is shown in Fig. 18, both regions 16 and 17 of the surface 13 are substantially in contact with die surface 18 of die insert 3 and die contact area between die component 2 and die insert 3 is reduced. Beyond approximatelj' 80° only the region 17 of die surface 13 is in contact widi die surface 18 of die insert 3 and the contact area between die component 2 and the insert 3 is at its smallest. However, the load between diem is at its smallest too. The largest loading between die two components 2 and 3 occurs between 0° and 30° of flexion when diey are both full congruent.

Implantation of the prosthesis is carried out in accordance wid the following steps. It should be noted that d e size of the tibial tray 1 and the femoral component 2 to be selected for a patient should be determined pre-operatively but should be verified during surgery using trial parts and templates. It will be appreciated diat die femoral component 2 will replace either the medial or lateral femoral condyle being removed while die tibial tray 1 defines the plane for the anterior-posterior and medial-lateral movement direction of the floating insert dependent on die tibial resection plane. During surgery, the tibia of the patient is prepared first. The orientation of the tibial resection is adjusted by an extramedullar_}' guide. Its distal end is placed around the patient's ankle and then it is aligned to die tibial axis. The proximal end of die extramedullar₎' guide is fixed to die tibia using die guide's built-in spikes or with pins through the cutting block. A tibial cutting block is also used and if no posterior slop is desired, the sagittal plane is adjusted by using the extramedulkry guide. The resection deptii is tiien determined using a stylus by touching the articular surface of die tibial plateau. The sagittal cut should be resected just medial to die ACL attachment point on die tibial spine hi order to maximize the size of die tibial base. The tibial tray 1 is fitted to die resected tibia and die keel 9 supports positioning and fixation of the platform 4 to the tibia. The oblique shape of the keel 9 facilitates die cutting of a groove in the resected tibia to enable the sliding of the tray 1 into position from anterior to posterior into the tibial resection. The position of die keel 9 is positioned roughly hi the centre of die tibial tray 1 and dierefore is roughly central beneath the insert 3 in order to increase die sttengdi of implant. The keel 9 also anchors d e tibial tray 1 into the tibial bone.

The tibial resection is used to measure the joint gap in botii flexion and extension, the extension gap being measured at 20° flexion. The difference between the extension gap and the flexion gap relates to possible cartilage damage or ligament disbalance and should be adjusted using spacers which are assembled widi die distal femoral resection guide. These correct the distal femoral cut so diat diere is a constant joint gap diroughout the whole range of motion. The size of the insert 3 is chosen according to die size of diis flexion gap.

Resection of die distal femur is performed in full extension using die same cutting block and an appropriate spacer. The posterior and die chamfer cut ate resected using a second cutting block, which also guides the drilling of the holes for die posts 15. The femoral component 2 is fitted to die resected femur using die posts 15, which are preferably aligned under 30° to the posterior cut and arc also perpendicular to die posterior-distal chamfer. Tliis facilitates the intra-opeiative placement of die component 2 and prevents its loosening in deep flexion. The femoral component 2 is then cemented into position to die resected distal femur. After fitment of both die tibial tray 1 and die femoral component 2, the insert 3 is pushed into position between diem.

Reference Numerals

1 Tibial tray

2 Femoral component

3 Floating insert

4 Platform

5 Proximal bearing surface

6 Distal fixation surface

7 Intercondylar wall

8 Cement pocket

9 Keel

10 Distal edge of keel

11 Apex of keel

12 Aperture through keel

13 Outer surface of femoral component

14 Fixation surface of femoral component

15 Posts

16 Anterior part of outer surface

17 Posterior part of outer surface

18 Femoral side of insert

19 Tibial side of insert

20 Posterior edge

21 Anterior edge

22 Intercondylar side

23 Superficial side

24 Posterior intercondylar corner

Al Angle between posterior and intercondylar sides of insert A2 Angle between anterioi^* and intercondylar sides of insert

D Depth of keel

Rl Radius of anterior part of femoral component

R2 Radius of posterior part of femoral component

R3 Radius in coronal plane

HI Posterior height of insert

H2 Anterior height of insert

Claims

1. A tibial tray (1) for a knee joint prosthesis comprising

a platform (4) including a proximal bearing surface (5) and a distal fixation surface (6); and

a keel (9) diat projects from the distal fixation surface (6) and that extends in an anterior-posterior direction with respect to die position of the tray (1) when in use;

characterised in diat die keel (9) is located centrally of the tibial tray (1) in a medial-lateral direction and is substantially planar in a sagittal place widi a distal edge (10) that extends obliquely widi respect to die proximal bearing surface (5) of die platform (4).

2. A tibial tray (1) as claimed in Claim 1, characterised in that die keel (9) has its deepest part towards the posterior aspect of the tray (1),

3. A tibial tray (1) as claimed in Claim 1 or Claim 2, characterised in that die keel (9) is substantially triangular is shape.

4. A tibial tray (1) as claimed in Claim 2, characterised in that an apex (11) of the triangular keel (9) is between 6 mm and 11mm from die distal fixation surface (6).

5. A tibial tray (1) as claimed in any of Claims 1 to 4, characterised in that an angle between the distal edge (10) of die keel (9) and die proximal bearing surface (5) is between 10° and 30° inclusive and is preferably approximately 17°.

6. A tibial tray (1) as claimed in any of Claims 1 to 5, characterised in that d e keel (9) extends in a sagittal plane over half die lengti of the anterior-posterior lengdi of the tray (1).

7. A tibial tray (1) as claimed in any of Claims 1 to 6, characterised in that die proximal bearing surface (5) is smoodi and generally planar.

8. A tibial tray (1) as claimed in any of Claims 1 to 7, characterised in that the distal fixation surface (6) of the platform (4) is configured for attachment to a tibia by a bone cement.

9. A tibial tray (1) as claimed in any of Claims 1 to 8, characterised in that the distal fixation surface (6) of the platform is provided with one or a plurality of cement pockets (8).

10. A tibial tray (1) as claimed in Claim 9, characterised in that each of the cement pockets (8) is aligned in an anterior-posterior direction.

11. A tibial tray (1) as claimed in any of Claims 1 to 10, characterised in that the distal fixation surface (6) of the platform is roughened.

12. A tibial tray (1) as claimed in any of Claims 1 to 11, characterised in that the platform (4) defines a wall (7) that projects in a proximal direction at an intercondylar edge of die proximal bearing surface (5).

13. A tibial tray (1) as claimed in Claim 12, characterised in that the wall (7) extends proximally, in use, in a sagittal plane.

14. A knee joint prosdiesis comprising a tibial tray (1) as claimed in any of Claims 1 to 13.

15. A prosthesis as claimed in Claim 1 , diat additionally comprises

a femoral component (2) adapted for attachment to a femur, and a floating insert (3) adapted to fit between the femoral component (2) and the tibial tray (1) when die prosthesis is implanted in a patient, die insert (3) having a femoral side (18) shaped to interface slidingly with an outer surface (13) of the femoral component (2) during flexion of the knee and a tibial side (19) shaped to interface slidingly with die proximal bearing surface (5) of the tibial tray (1),

16. A prosthesis as claimed in Claim 15, characterised in that the insert (3) is not symmetric about a sagittal plane.

17. A prosdiesis as claimed in Claim 16, characterised in that the insert (3) has a intercondylar side (22) that is longer in length dian an opposite superficial side

(23) .

18. A prosdiesis as claimed in Claim 16 or Claim 17, characterised in diat a corner

(24) at a posterior end of die intercondylar side (22) of die insert (3) is extended to project learwardly,

1 . A prosdiesis as claimed in any of Claims 16 to 18, characterised in diat an angle (Al) between the intercondylar side (22) and a posterior side of the insert (3) is less than 90°.

20. A prosdiesis as claimed in any of Claims 15 to 19, characterised in that corners between a superficial side (23) of the insert (3) and its posterior and anterior sides are rounded.

21. A prosdiesis as claimed in any of Claims 15 to 20, characterised in that a surface of die dbial side (1 ) of die insert (3) is smoodi and generally planar.

22. A prosthesis as claimed in any of Claims 15 to 21, characterised in diat an anterior-posterior profile of die insert (3) is substantially wedge-shaped with die anterior height (H2) greater than the posterior height (HI).

23. A prosthesis as claimed in any of Claims 15 to 22, characterised in diat in die sagittal plane the difference in height between a deepest point of die femoral side (18) of die insert (3) and a posterior edge (20) of die femoral side (18) of die insert (3) is no greater than 3 mm and is preferably of die order of 2mm.

24. A prosthesis as claimed in any of Claims 15 to 23, characterised in that in die sagittal plane the difference in height between a deepest point of the femoral side (18) of the insert (3) and an anterior edge (21) of the femoral side (18) of the insert is between 2mm and 6 mm inclusive and is preferably of the order of 4 mm.

25. A prosthesis as claimed in any of Claims 15 to 24, characterised in that said outer surface (13) of the femoral component (2) defines two regions (16, 17) for flexion rotation in a sagittal plane of which a first region (16) has a first radius of curvature (Rl) and a second region (17) has a second radius of curvature (R2), the first radius of cur ature (Rl) being larger than the second radius of curvature (R2), and in that the surface of the femoral side (18) of die insert (3) has substantially the same radius of curvature in the sagittal plane as the first radius of curvature (Rl) of the femoral component.

26. A prosthesis as claimed in any of Claims 15 to 25, characterised in that said outer surface (13) of the femoral component (2) has a third radius of curvature (R3) for varus/valgus rotation in a coronal plane, and in that the surface of the femoral side (18) of the insert (3) has substantially the same radius of curvature in the coronal plane as the third radius of curvature (R3) of die femoral component (2).

27. A prosdiesis as claimed in any of Claims 15 to 26, characterised in that it comprises a unicondylar prosthetic device.