fig1 shows a perspective view of a wound dressing 10 comprised of a non - woven web of elongated hydrophilic microfibers 11 forming a homeostasis media having a backing 12 to enhance handling of the wound dressing . backing 12 , which is a convenience in handling , is optional and need not be used . the microfibers 11 can have a solid or micro porous surface . the microfibers can be formed into a non - woven wound dressing without the use of adhesives or other dissimilar materials . in the preferred embodiment , the microfibers are made of biocompatible polymeric materials , and formed directly into a non - woven sheet which can be used as a blood clot inducing wound dressing . the microfiber surfaces can be held together by pressue , bonded or fused together at contact regions between adjacent microfibers during the manufacturing process which inhibits the microfibers from shedding or falling into the wound during application of the wound dressing 11 . bonding the microfibers to each other to avoid shedding thus inhibiting or preventing contamination of the wound from individual microfibers . the use of microfibers in the present invention allows the non - woven sheet to be very pliable and flexible which allows it to easily conform to the contour or shape of the wound site . as such the non - woven sheet may be made into various configurations for specific types of wounds such as wraps , pads , bandages , plugs , custom shapes or other configurations similar to conventional wound dressing . the present invention can be supplied as rolls , flat sheets or die cut pieces of various shapes and sizes . in addition , these non - woven sheet can be of various thicknesses depending on the needs of the application . microfiber bonding , can be accomplished by one or more methods known in art including but not limited to chemical , resin , thermal , pressure bonding . bonding of fibers is accomplished when the fibers ( which may be coated with a resin or uncoated ) are in molten , semi - molten , or sticky state and touching . this may be accomplished during the manufacturing of the fibers or after by use of the methods known in the art for bonding polymers . the microfibers 11 are made from a hydrophilic material to promote rapid wicking and drawing liquids from blood ( i . e . water , plasma and serum ) from blood at a wound site to concentrate platelets and clotting factors . in order to increase the wetability and wicking characteristics of the microfibers it is preferred that the surface tension of the microfibers be at least 50 dynes / cm , and preferably , greater than 70 dynes / cm . the microfibers are made from hydrophilic material , and preferably from polymers which are biocompatible and bioabsorbable . suitable hydrophilic materials include polyglycolic acid , polylactic acid , and other polymers commonly used for sutures and other applications requiring bioabsorbable materials . in order to increase wetability of the hydrophilic materials the polymers can be modified by sulphonation , chemical addition , grafting , or other techniques used to modify polymers . fig2 shows an enlarged view of a portion of wound dressing 10 revealing individual microfibers 11 with open regions or pores 15 extending between adjacent microfibers . the microfibers 11 are secured to each other at contact regions between adjacent microfibers to form a self - adhering homeostasis media with the pores formed by the gaps between the microfibers . in general , the size of pores 15 of the homeostasis media should be small enough to prevent platelets from wicking into the media but allow blood liquid to wick into the media . by inhibiting or preventing platelets from wicking into the media causes the platelets and other clotting factors to accumulate and concentrate on the surface of the media and thus initiate the clotting process . as platelets are approximately , 2 to 4 micrometers in diameter , the effective pore size of the hemostatic media should generally be less than 4 micrometers and , preferably , less than 2 micrometers in size to block or inhibit the platelets from entering the pores . in general the pore size of the hemostatic media made from microfibers is directly related to the diameter of the microfibers used . for example , to make a hemostatic media having a pore size of about 2 micrometers the average fiber size of the media are approximately 2 micrometers or less in diameter . in general , the microfibers 11 of the present invention are generally 7 to 34 times smaller in diameter than the fibers proposed by roth u . s . pat . no . 3 , 937 , 223 or schmitt u . s . pat . no . 3 , 620 , 218 . for a given mass of fibrous mat , smaller pore sizes can be achieved by using smaller fibers . smaller fibers are advantageous for several reasons : 1 ) smaller fibers enable more surface area in given fibrous mat volume . 2 ) smaller fibers enable creation of smaller pores and 3 ) smaller fibers enable more open void volume for a given fibrous mat volume . since the surface area to volume ratio is proportional to 1 /( fiber diameter ), the larger the fiber diameter , the smaller the surface area to volume ratio . it is advantageous to have a large surface area to volume ratio for a hydrophilic microfiber as the rate of adsorption of blood liquid into a hydrophilic microfiber increases with increase surface area and smaller pores . at the same time , the small size pores are able to increase the capillary effect to allow wetable fluid to wick from the wound to the hydrophilic microfibers . at the same time the fluid is being wicked through the pores the small pore size of the homeostatic media inhibits or prevents platelets , red blood cells , and white blood cells in the blood from being passing into the homeostatic media . consequently , the blood cells including platelets and clotting factors accumulate on the surface of the media and proximate the wound to initiate clotting of blood . the microfibers in the present invention include fibers that are hydrophilic to cause wicking of the blood fluids ( primarily plasma / serum ) into the fibrous mat . the higher the fibers surface tension the greater the wetability and wicking tendency of the fibrous mat will be . it is advantageous to have fibers with a surface tension of at least 50 dynes / centimeter to readily wet the fibers and cause rapid and substantial wicking of the fluid into the fibrous mat . while pore size and fiber surface tension are important factors in the promoting wicking and clotting , the pore size is related to the average fiber diameter . by having the average fiber diameter approximately the same size as the platelets or smaller the average fiber diameter of the fibrous mat can be less than 4 microns and preferably less than 2 microns and more preferably less than 1 micron . if desired the fibrous mat can also include hemostatic particles such as starch , collagen , oxidized cellulose , or others known in the art . these particles can be embedded in the surface of the fibers or encapsulated within the fibers themselves . if desired the fibrous mat can also include a hemostatic agents such as calcium , fibrinogen , thrombin , factor vii , factor viii or others know in the art to accelerate clotting . if desired , the surface area of the microfibers can be enhanced in several ways . for example , smaller diameter microfibers can be used or the microfibers can be made in non - circular shapes such as a microfiber having a cross section with 3 or more lobes as shown in fig3 . that is , microfiber 20 has a first longitudinal lobe 22 , a second longitudinal lobe 23 and a third longitudinal lobe 24 . the fold or recessed region 24 can provide a region for adding homeostatic agent thereto . smaller diameter microfibers and microfibers having non - circular shapes provide greater surface area per unit volume as well as enhancing the wicking capabilities . if desired , the channels created by the lobes on the microfibers can also be used to retain hemostatic particles such as starch , collagen , oxidized cellulose , or others known in the art , or also hemostatic agents or clotting accelerators such as calcium , fibrinogen , thrombin , factor vii , factor viii or others know in the art . the surface area of the microfibers can also be enhanced by creating a three - dimension texture on the surface of the microfibers during the manufacture of the microfibers . the texture can take the form of impressions , dimples , cracks , or other geometric shapes . these cracks or impressions , which can extend deep into the fiber , increase the surface area even further , thus creating greater surface area and increased wicking capabilities . fig4 shows a perspective view of a hydrophilic microfiber having a set of embedded particles 26 and a set of cracks or fissures 27 that further increase the exterior surface area of the hydrophilic fibers . the methods of manufacturing of the present invention include one or more of those known in the art including but not limited to melt blown , thermal bonded , chemical bonded , resin bonded , spun bonded , spunmelt bonded , carded , air laid , wet laid , spunlaced , hydroentangled , electro - spinning process or processes . the microfibers can be extruded through a small opening in a die as a molten polymer and can be stretched or attenuated by blowing high velocity air co - currently with the microfibers while they are still warm . the average pore diameter ( viscous - flow - average ) d p is equal to the square root of d p = average pore diameter z = media thickness t = tortuosity ( assumed to be 1 / ε for the purposes of the invention ) ε = porosity of the medium μ = viscosity v = face velocity δp = pressure drop across the medium for example , the average pore diameter can be specified to be less than certain value . the average pore size necessary to stop or impede blood cells and to concentrate clotting factors at the surface of the fibrous mat should be less than 4 microns and preferably less than 2 micron and more preferably less than 1 micron . the microfibers can also be formed by the extrusion of a solution a polymer and a solvent through small openings in a die . this type of extrusion lowers the viscosity of the polymer solution and makes it easier to manufacture smaller microfibers . high velocity air may also be used to stretch or attenuate the microfibers . the solvent is flashed off or extracted from the microfibers in a secondary process . to enhance the surface area mechanical stresses or cracks on the surface of the microfibers can be made by secondary processes such as chemical etching , radiation , temperature fracturing , or other techniques known in the art . if desired , hemostatic particles or hemostatic agents can be mixed in with the polymer prior to the extrusion process which results in the particles or agents being embedded within the microfibers . the addition of hemostatic particles or agents to the hydrophilic microfibers can further enhance clotting by increasing the water absorbing properties of the microfibers at the blood / fiber interface . while not as desirable , the hemostatic particles or hemostatic agents can be embedded on the surface of the microfibers while the microfibers are being formed and are still semi - molten . embedding hemostatic agents during formation of the microfibers is preferred over the use of adhesives , binders or other techniques used in the gauze / particle devices . in the embedding process the particles are embedded in the surface of the microfibers while the microfibers are in semi - molten condition . the embedding process causes the hemostatic particle or hemostatic agents to be physically retained without the use of binders , adhesives or other means once the polymer cools . the embedding during a semi - molten state of the polymer creates a firm grip on the particles and significantly lessens the chances of having the particles released from the surface or internal areas of the media matrix . thus in one embodiment a feature of the present invention is to provide a wound dressing which does not have loose particles , is made from microfibers which are secured to each other and have a pore size for enhancing blood clotting , has a high degree of open are so as to enhance clotting , is flexible and conforms to the wound site , is biocompatible and bioabsorable , can be made of only one material of construction ( i . e . one polymer ), and is easy and less costly to manufacture . other embodiments of the wound dressing comprise a fibrous media wherein a surface of a single hydrophilic microfiber is arranged to form a set of pores in a fibrous media with the set of pores having a pore size sufficiently small to inhibit wicking platelets from a wound into the media via the set of pores while the hydrophilic microfiber enhances wicking of water threrethrough . in other embodiments the microfibers can be held proximate each other without adhesion to provide a mat that can inhibit wicking of a platelet from a wound into the mat .
a wound dressing and a method for enhancing the clotting comprising a plurality of hydrophilic microfibers bonded to each other to form a mat with the plurality of microfibers having a pore size sufficiently small to inhibit wicking platelets from a wound into the microfibers so that when applied to a wound the blood coagulates and the microfibers remain external to the wound .