the pressure - forming steps of the invention may be effected by blow moulding or vacuum forming . ( a ) extrusion blow moulding -- is a process whereby a cylindrical parison of polymer in its hot , plastic state is introduced into a two piece tool that when closed , simultaneously seals the bottom of the parison and creates the means at the top of the tool for air to be blown into the top of the parison so that the parison inflates to follow the shape of the inner cavity of the tool . this type of blow moulding will result in a seam where the parison is sealed by the tool . the process allows for single layer or multi - layer structures to be formed ( co - extrusion ). ( b ) stretch blow moulding -- is similar to conventional extrusion blow moulding but a mechanism is incorporated into the tooling that mechanically stretches the parison along its length prior to the blowing stage . this mechanical stretching ensures bi - axial orientation of the polymer with associated improvements in the mechanical properties of the end product . ( c ) pre - form blow moulding -- is a process whereby a preformed shape is made by injection moulding or polymer dipping or similar and in a secondary process , the pre - form is heated and blown within a cavity mould into the required end product . vacuum forming requires the provision of negative pressure to the opposed surface of the parison and has the advantage of producing a seamless product . fig1 shows a cross - section through a material 1 according to an embodiment of the invention . the material comprises a plurality of platelets 2 suspended in an elastomer 3 . the platelets are dispersed in a generally homogenous manner in the elastomer . whilst the platelets may be formed of any suitable material , e . g . metal or plastics , fig1 shows ceramic material and in particular , a ceramic silicate . aluminia silicates are also a preferred choice . the elastomer may be any suitable material for example , polyethylene , polypropylene and polyurethane . the elastomer provides the material with a degree of flexibility in all directions and should have a flexural modulus of & lt ; 300 mpa and preferably & lt ; 30 mpa . it will be noted that the platelets are generally aligned in the material such that at least a majority lie parallel to the upper and lower surfaces 4 and 5 , also at least the majority of the platelets overlap one another so as to form a continuous barrier across the material . the overlapped nature of the platelets strengthens the barrier against puncture . the thickness or density of the material can be varied to meet particular anti - puncture requirements as desired . for the preferred embodiment of surgeon &# 39 ; s glove as shown in fig1 the material is arranged to be of the order of 250 microns thick thereby giving the required flexibility and touch sensibility . the high aspect platelets themselves are preferably 10 to 15 microns across and 1 to 5 microns deep . with these characteristics , the material can withstand an os4 cutting suture needle , for example 50 mm long and 0 . 4 mm diameter , loading of 600 to 1200 grams . of course for different applications , e . g . garden gloves , etc ., these variables can be altered as required . as shown in fig1 there are a number of horizontally extending voids . these would normally be occupied by ceramic platelets but these were removed during preparation by polishing of the material for photomicrography . the material may be provided at specific areas only of a garment . for example a glove may be provided with more or less reinforcement only at certain areas . preferably an entire garment can be manufactured from the material but by means of co - extrusion , certain areas only may be provided with the ceramic reinforcement . a preferred method of production of the glove is shown schematically in fig2 . as shown , the liquid elastomer 3 has mixed into it microsized , preferably high aspect ratio , ceramic platelets 2 in powdered form . the resulting mixture is poured into a plug - shape mould 6 such that the mixture can initially set in the shape of a thin wall tube . of course , any suitable shape may be formed . thereafter a setting pressure p is preferably applied to the tube at a suitable pressure , such pressure preferably having a preliminary effecting in aligning the platelets so that they begin to become aligned substantially parallel to the surface of the material . the application of pressure to align the platelets of course could be provided as a completely separate step to that of the forming of the parison . in this regard , it will be appreciated that the method of manufacture may include curing the parison by any suitable means . these may include the inclusion of an additive , e . g . an accelerating agent and / or by use of heat and / or pressure . use of heat and / or pressure may however may have the above - mentioned advantageous effect in preliminarily aligning the platelets . the shaped tube is then heated with heater 7 and blow moulded via mould 12 into the shape of a glove 8 . during the blow moulding treatment , the material is compacted a second time under pressure to ensure alignment of at least a majority of the platelets . whilst a method of manufacturing a glove is described above , the same method can of course be used to produce alternative items . in an alternative method of producing articles of clothing in the present invention , the parison manufactured as produced above may be collapsed to form a substantially flat envelope of material . the profile of the desired article , e . g . a glove , can then be cut from the envelope using any suitable means , for example a laser . the use of a laser is particularly advantageous in that the edges of the opposed faces of the clothing article are fused together along the profile whilst being cut from the collapsed parison . in a preferred method for the production of a glove in accordance with the present invention , the method of manufacture may be as follows : mixture of polyurethane polymer ( estane ; registered trade mark ) is admixed with various mixes of ceramic platelets for example , 0 %, 10 %, 20 % and most preferably 30 % by weight . the resultant mixture is then heated and formed into rods and the rods are cut into pellets for further processing . using other polymers , it is possible to load the material with up to 60 % by weight or even higher if the base polymer is highly elastermeric . this is because the lower the flexural modulus of the polymer , the higher the loading of platelets which is possible . these are all then melted and passed through a conventional screw extruder to form a tube shaped parison . the parison may alternatively be made by injection moulding . the so formed parison may be stored as such for future use for a considerable period . subsequently the final shape , in this case a surgeon &# 39 ; s glove , can be formed by moulding . to this end , the parison is subjected to a primary formation step in which the tubular parison is closed at its remote end and a glove - shaped pre - form is formed . the glove - shaped pre - form is then introduced into a final blow moulding step and subjected to biaxial stretch blow moulding by heat and pressure to form the final glove shape , before being removed from the mould for cooling . as the step of blow moulding materials such as bottles is well known , the discovery by the applicant that significantly improved products could be produced by using blow moulding techniques for the formation of a product such as puncture resistant gloves incorporating ceramic particles is a significant advance since it leads to the production of articles having very much improved puncture resistant properties . the materials formed by the above process were then tested against a commercially available latex glove , again the du puy ( medak ) glove mentioned previously and against a glove material formed by traditional extrusion moulding techniques . the results are shown in fig5 . from this figure it will be seen that at 20 % ceramic platelets , a blow moulded estane glove having a final thickness of about 200 μm withstood a loading of between 600 to 800 grams while at the same thickness and using the same starting material , an extruded product could only withstand a static loading of the order of 100 - 200 grams . the &# 34 ; medak &# 34 ; glove product had a thickness of about 1200 μm and withstood a loading of 600 grams , while at that thickness the product in accordance of the present invention withstood a loading of between about 800 and 1400 grams . whereas at 1200 μm the thickness of the inventive glove material is too great for surgical use , it is useful for gardening and industrial gloves and at that thickness is roughly twice as penetration resistant as the medak glove . at 400 μm , the efficiency of the inventive product is of the order of four times that of the prior art result . the gloves as shown in fig5 are made in accordance with the product as shown in fig1 . on the scale shown in fig1 a suture needle tip is in excess of one half of the horizontal transverse section as shown . it follows that the penetration of such a needle , however sharp , must be resisted by a significant number of horizontally overlapping platelets . one of the problems however with the inventive glove product is that at the material surface the ceramic platelets tend to be dislodged . this happens because the platelets are either at the surfaces or immediately adjacent to them . this results in &# 34 ; dusty &# 34 ; surfaces which can become semi - porous . this does not matter for a material intended for industrial gloves for example , which has a thickness of 1200 μm , but it could be a significant feature with regard to the surfaces of gloves having an overall thickness of 250 to 400 μm . to address this , it is often desirable to overlay the parison with a layer of the same or a compatible polymer or elastomer simultaneously with parison formation by , coextrusion . this allows a fine layer of polymeric material of about 5 to 10 μm to overlay the inventive material . it will also be appreciated that for different purposes , the relative thickness and purpose of the layers can be altered at will to provide , for example , a relatively thick platelet free outer layer ( or vice - versa ). for example the inner and outer surfaces of the puncture resistant material in accordance with the present invention can thus be sealed and the outer surface can be made to have different characteristics than the inner surface . thus the outer surface may be made to assist gripping whereas the inner surface may be made with a low friction surface to allow the hand to easily don the glove . fig3 shows in perspective a pair of surgeon &# 39 ; s hands , namely left hand 9 and right hand 10 . on each hand there are shown a number of dots representing areas particularly vulnerable to needlestick injury . in this connection it has been reported that of all hospital related injuries to employees , the highest percentage ( 35 %) is caused by needlestick and other sharp object ( sharps ) injuries , ( british journal of nursing , 1992 , vol 1 , no 8 , pages 389 to 390 ). furthermore form a study reported in the publication british journal of surgery 1988 , vol 75 , april , pages 314 to 316 , the overall perforation rate of surgical gloves used in general surgical procedures was 37 . 5 %. fig4 shows a glove made according to the preferred method described in relation to fig2 . hatched areas 11 represent portions on such a glove which may be additionally reinforced , bearing in mind the vulnerable areas shown in fig3 . these areas may alternatively represent portions of material according to the preferred embodiments of the invention , which are applied to existing gloves to increase their resistance to puncture in the vulnerable areas . the production of a seamless pre - form and a glove formed therefrom was effected as shown in fig6 and 7 by : ( 1 ) creating a one piece female tool ( 20 ) into which the pre - form is blown . this does not create seams or flash . the tool can be cast and not machined and therefore is relatively inexpensive to produce . ( 2 ) a pre - form male tool ( 22 ) is used to create a pre - form ( 21 ) of the polymer / platelet composite from either a hot melt or solvented polymer base . the pre - form ( 21 ) is of a size , relative to the female tool ( 20 ), that will allow suitable biaxial orientation of the platelet / polymer composite to occur during the blowing or vacuum forming phase , thus the allowed extension should be equal to , or exceed 1 . 25 . ( 3 ) when the pre - form ( 21 ), still attached to the pre - form tool ( 22 ), is inserted into the female tool , an air seal is formed at the neck ( 23 ) of the female tool ( wrist end ) and the pre - form is inflated via a device in the pre - form tool . a vent for air trapped in the cavity of the female tool is provided if necessary . since the pre - form and the pre - form tool extend into the female tool to a point where the pre - form finger ( 24 ) and thumb ( 25 ) sections extend into the top of their respective finger ( 26 ) and thumb ( 27 ) cavities of the female tool , when the pressure applying phase commences , inflation of the pre - form must occur with the fingers and thumb extending into their respective cavities . thus the need to stretch blow is eliminated . ( 4 ) after forming , the pre - form tool ( 22 ) is withdrawn ( since it is of smaller diameter ) through the neck ( 23 ) of the female tool . the formed glove is then sucked out of the female tool ready for packaging etc . since the only flash generated is at the wrist end of the glove that can be quickly removed before the glove is sucked out of the tool . the invention applies therefore to a method for the manufacture of a puncture resistant sheet , to a puncture resistant article formed thereby and to a parison therefor .
the invention provides a puncture resistant polymeric sheet material comprising a plurality of discrete platelets disposed substantially parallel to the plane of the sheet material in an overlapping interrelation , wherein the disposition of the platelets in the sheet material has been effected by pressure - forming . as shown in fig . 5 , pressure - forming techniques result in an decrease in penetration by a factor of up to four .