2 THE PREPARATION OF ULTRA HIGH MOLECULAR WEIGHT

3 POLYETHYLENE MORPHOLOGIES OF TOTALLY FUSED PARTICLES WITH SUPERIOR MECHANICAL PERFORMANCE

5

6 _i2I C .__ __ _. __.-__ A T JE O N

7

8 Cross References to Related Applications This application is a continuation-in-part of I _Q application Serial No. 586,796, filed March 6, 1984.

H Co-pending patent application No. 578,171, filed

12 February 8, 1984, relates to a solid state deformation

13 process for achieving the production of high modulus and

14 high-strength polymers in simple and complex shapes at

15 rapid output rates and moderate processing conditions.

16

17 Field of Invention

•i This invention relates to a novel type of ultra-

• _j q high-molecular-weight polyethylene with superior modulus elastic response performance and the method of making

22 Ultra-high molecular weight polyethylene has been

23 defined by ASTM as those linear polyethylenes which have a

2 relative viscosity of 2.3 or greater at a solution con-

25 centration of 0.05% at 125°C. in decahydronaphthalene. The nominal weight-average molecular weight is several 27 million, usually from three to six million.

28 9 Background of the Invention . _Q Various polymer systems have been investigated for such uses as the preparation of artificial prostheses for 2 biomedical, particularly orthopedic applications. The 3 objective has usually been to dupl-icate the mechanical 4 properties of the natural counterparts and to meet the 5 requirements of tissue biocompatibility. For example, the 5 preparation of artificial tendons has been pursued basi- 7 cally by the construction of composite structures of Q

1 fiber-reinforced elastomers, such as poly(ethylene tereph-

2 thalate) in silicone rubber. Silk and metal fibers have

3 also been used as components in such prostheses. The ^ fabrication of tapes and fiber meshes using conventional polymers, e.g., nylon, dacron, and polyethylene has also

* been explored. In the latter case, however, nylon has been

* found to degrade in vivo? dacrons have been found to fail ° in tissue ingrowth tests; and conventional polyethylene 9 when strained in the working range of human tendons ( 3% " strain) , has been unsatisfactory both in its elastic H recovery (80-90%) and in the time needed for complete 12 recovery ( 5 min.) —two important factors in the design - of artificial tendons, 14- Ligament fabrication has been pursued by the

15 design of artificial preparations utilizing ultra-high-

16 molecular-weight polyethylene. Ultra-high molecular weight

17 polyethylene, in contrast to the conventional high-density 8 polyethylenes having average molecular weight up to about

19 400,000, has an extremely high molecular weight— ypically 0 2 to 6 million—and is intractable. The polymer is 1 supplied as fine powder and is processed into various 2 profiles using ^" compression molding and ram extrusion

23 processes. However,, studies made heretofore have suggested ** ^* that the ultra-high molecular weight polyethylene 5 structures made by such processes do not possess adequate 6 yield, creep, and fatigue properties to meet the require- 7 ments of bio edical applications, apparently because of 8 poor interparticle fusion of the powder particles in the 9 raw material during its processing. More recently, new 0 processing systems, including ultra-high speed mixing 1 systems and radio-frequency heating, have been used in 2 injection molding practices to produce ultra-high molecu- 3 la weight products. However, the products of such ^- processes are obtained also in a temperature range 5 (360-380 o _F . 182 - 193θC.) in which it has been found 6 that complete fusion of the powder particles does not 7 occur. Furthermore, radio-frequency heating, an effective

process for heating polymers such as nylons, PVC, and PVF2

2 that have polar molecules to respond to radio-frequency

3 energy is impractical for non-polar polymers such as poly-

4 ethylene. Radio-frequency heating of such polymers can * occur by incorporating in the polymer agents such as 6 Frequon (a trademark of the Phillips Chemical Co.) which ' are sensitive to radio frequency. However, the use of

8 additives in the polymer, which is known to be bio-

9 compatible, may have adverse effects in meeting the

10 requirements of tissue biocompatibility in biomedical 1 applications. 2 3 Summary of the Invention ^* This invention provides the complete fusion of 5 powder particles of ultra-high molecular weight poly- 6 ethylene in an hitherto unexplored temperature range, 7 resulting in a homogeneously melt crystallized morphology 8 with no grain memory of the powder particles and the 9 preparation of an anisotropic morphology with significant- 0 y enhanced modulus and superior elastic response perform- 1 ance by solid state deformation techniques. The present invention provides a homogeneously 3 melt-crystallized morphology of ultra-high molecular poly- 4 ethylene obtained by complete fusion of the powder 5 particles of the raw material in a temperature range in 6 which the powder particles fuse completely and have no 7 memory of their granular structure prior to melting and 8 during the inadequate melting which is practiced in 9 currently used processes. The mechanical performance of 0 such homogeneous melt crystallized morphologies of ultra- 1 high molecular weight polyethylene are superior to the 2 properties of commercially available products of ultra- 3 h gh molecular weight polyethylene. ^* * This invention provides also the preparation of an 5 anisotropic morphology of ultra-high molecular weight 6 polyethylene with significantly enhanced modulus and 7 superior elastic response performance by the solid state

1 deformation techniques of drawing and extrusion through an

2 extrusion rolling die. This performance has been demon-

3 strated both in laboratory testing and in vivo functional 4- loads for bio edical applications.

^* According to the present invention, the prepara- ° tion of the anisotropic morphology of ultra-high olec- ular-weight polyethylene comprises the steps of (1) pre- paring initially a uniform semicrystalline morphology by ^* * compression-molding an ultra-high molecular-weight poly- " ethylene melt in a temperature range in which the melt has 1 no memory of the granular nature of the original powder, 2 and (2) solid-state deforming the so-produced uniformly 3 melt-crystallized morphology by conventional drawing or by 4 extruding it through an extrusion rolling die at a 5 temperature preferably near but below its crystalline 6 melting point and at a deformation ratio of 5-8. The 7 deformation ratio is determined by the displacement of 8 printed markers or fiducial marks on the surface of the drawn or extruded specimen or the cross-sectional areas of the samples before and after drawing or extrusion.

Brief Descriptio of the Drawing Fig. 1 is a graph showing the stress-elongation behavior at ambient temperature of two compression-molded specimens of ultra-high molecular weight polyethylene, one molded at 180°C and the other according to the present invention, at 320OC.

Fig. 2 is a similar graph contrasting the stress- strain behavior of three specimens of five-times-drawn ultra-high molecular weight polyethylene obtained by s&lid-state deforming of compression molded specimens at 180OC, .and 210°C, and, according to the present - invention, at 320°C.

^• ^ Fig. 3 is a similar drawing, showing the stress-

2 strain behavior under cyclic load tests at ambient

3 temperatures of five-times-drawn ultra-high molecular ~* weight polyethylene morphologies obtained by solid-state deformation of a compression-molded specimen at 180°C

6 and, according to the present invention, at 320°C. 7 Fig. 4 is a diagrammatic cross-sectional view of a flexor tendon and related parts, employing the principles 0 of this invention, indicating the tendon-bone and the 1 muscle-tendon functions and the body of the tendon which was truncated to insert and suture the artificial tendon of ultra-high molecular weight polyethylene of this invention.

Description of Some Preferred Embodiments of the Invention An ultra-high-molecular-weight polyethylene melt, in which the powder particles fuse completely and lose memory of their granular structure in the original powder stock, is achieved by heating the powder stock or partially fused, melt-crystallized morphology having granular memory — in the absence of oxygen to avoid degradation, e.g., under nitrogen — in a temperature - range above 220°C. and below 340OC. the latter being the temperature at which excessive decomposition occurs under nitrogen. Isobaric heating at 320°C. under a compression load of 1500-2000 lbs. for 10 minutes followed by heating at 150OC. under a load of 12000-14000 lbs. for an additional 10 minutes and cooling to ambient under the same compression conditions results in a uniform or homogeneous melt-crystallized morphology with no grain memory. The resultant ultra-high molecular weight poly- ethylene morphology has superior mechanical performance in - comparison to currently available products which are fabricated typically in the temperature range of 180-210°C and under similar pressure conditions.

Prior literature dictates that under these temper- ature and pressure conditions the powder particles should fuse completely. (The equilibrium melting temperature of ^** ideal crystals of polyethylene is 141.4°C.) However, in the case of ultra-high molecular weight polyethylene such processing conditions result in a partial fusion as mani- fested from the grain memory of the original powder particles and the diminished mechanical properties. Complete fusion of the powder particles of ultra-high molecular weight polyethylene and consequently a uniform melt-crystallized morphology occurs by heating above 220°C. and results in superior mechanical properties in comparison to the properties exhibited by the prepared - morphologies below 220 ^O C., i.e., 180 - 210°C. Alternatively, a partially fused, melt-crystallized morphology with granular memory, typically obtained at temperatures below 220°C, can be heated above 220°C. to obtain the complete fusion of this invention. The partial fusion of the powder particles below 220°C. arises from the high melt viscosity (in the temperature range 145 - 210°C.) which hinders the for a- tion of a molecular network between powder particles and to the high degree of physical entanglements which hinder - chain mobility during the compression molding process; effective chain interpenetration between powder particles can occur upon heating the raw powder stock or a partially fused melt-crystallized stock with granular memory above 220 ^O C. where the melt viscosity is significantly lower. As shown in Fig. 1, the presence of a molecular network between powder particles in the compression molded specimen at 320°C results in a significantly higher slope o stress to extension and strength to break (150 MPa) , in comparison to a specimen molded at 180°C. which is com- - prised of partially fused powder particles and which fractured at 35-40 MPa.

1 Solid-state deformation of such homogeneously

2 melt-crystallized morphologies previously prepared by

3 compression molding at 320°C. take place by drawing or 4- extrusion through an extrusion rolling die at 130°C and a deformation ratio 5-8 and result in anisotropic morpholo- gies with superior mechanical properties in comparison to

7 the five-times-drawn morphologies obtained by solid-state deformation of compression-molded at 180-200°C. For exara-

9 pie, as shown in Fig. 2, the slope of stress to elongation of an anisotropic morphology of a five-times-drawn ultra- 1 high molecular weight polyethylene sample prepared by 2 compression molding at 320°C, is considerably higher than 3 the slope of a five-times-drawn sample from a compression molded specimen at 210°C, and significantly higher than the slope of a five-times-drawn sample from a compression molded specimen at 180°C, evidently reflecting the higher degree of interparticle chain penetration which occurs by compression molding at higher temperatures. The overall increase in the slope of load-to- elongation observed in Fig. 2, in comparison to the un- drawn morphologies in Fig. 1, is associated with the chain extension and orientation of the five-times-drawn morphol- ogies. The five-times-drawn morphologies from specimens - compression molded at 320°C. have a Young modulus of 5-6 GPa,and in cyclic load tests under 40-45 MPa for testing _U to 1 hour they deform practically elastically (see Fig. 3). on the contrary, as also shown in Fig. 3, the five- times-drawn morphologies from specimens compression molded at 180°C have a low Young modulus (0.7-0.8 GPa) and in cyclic load tests under the same conditions undergo a maximum residual elongation greater than 3%. Tests In vivo indicate that artificial tendons made by this process can be sutured to the natural tendon - segments readily and without fibrillation. It is signifi- cant that the ultra-high-molecular-weight polyethylene anisotropic morphologies in this invention do not exhibit a tendency to fibrillation, for this is in contrast to

the fibrillation observed with conventional-molecular- weight (60,000 to 400,000) polyethylene analogues. Aniso- tropic products are strong only in the drawn direction in ^* which the molecular chains are oriented and connected by covalent bonds but are extremely weak in their lateral direction because the chains are connected by weak Van der waa s forces, and consequently when a load is applied perpendicularly to the direction of chain orientation they tend to fibrillate along the chain direction. Although cross-linking by radiation or chemical additives have been used to alleviate the occurrence of fibrillation, the resistance to fibrillation of the ultra-high molecular weight polyethylene anisotropic morphology in this - invention is due to the excessive amount of physical entanglement in the so-prepared initially homogeneous melt crystallized morphology. Artificial tendons made according to the present invention exhibit very satisfactory anastomosis after an observation period of six weeks, and they replicate the properties of the natural tendons. For example, they have been found to replicate the properties of the tendon (Flexor Hollucis ^* longus) of a dog weighing approximately 70 pounds, as demonstrated by the complete mobility of the 3 ₀ g during the six-week testing period. A lateral view of a flexor tendon indicating the tendon-bone and the musculo-tendon junctions and the body of the tendon which was truncated to insert and suture the artificial tendon of ultra-high molecular weight polyethylene is shown in Fig. 4. The present invention also includes within its scope the use of the isotropic (the initially homogeneous melt-crystallized morphology, prepared from either a raw powder stock or a partially fused me ^' lt-crystallized stock - with granular memory, prior to drawing or extrusion) and anisotropic ultra-high-molecular-weight polyethylene morphologies in other biomedical applications, e.g., ligament prostheses in which a high elastic recovery and a

small percent strain under high load requirements are necessary. Furthermore, the homogeneity of the morphologies in this invention versus the partially fused ^* morphologies used to date, is important in eliminating the fatigue failure observed with orthopedic prostheses which are.fab icated from partially fused morphologies and also in the fabrication of orthopedic prostheses with abrasion resistance uses such as joints and intervertebral disks. Other applications on which the homogeneity of the morphologies in this invention is important, is in the fabrication of industrial parts with abrasion resistance uses such as bearings, sprockets, gaskets, ball valve seats, conveyor belt parts and other industrial parts currently made from metal. To those skilled in the art to which this inven- tion relates, many changes in construction and widely differing embodiments and applications of the invention will suggest themselves without departing from the spirit and scope of the invention. The disclosures and the des- criptions herein are purely illustrative and are not intended to be in any sense limiting.