Hemostatic Device and Method

Abstract

A hemostatic tablet preferably including potassium ferrate and a cation ion exchange resin pressure formed into a tablet for delivery to a bleeding wound. The tablet improves the rate of adhesion to a bleeding wound surface, and allows a significantly greater and more uniform pressure to be exerted by manual compression of the tablet on the wound site, as compared to that of a thin layer of scattered hemostatic powder. After the seal is formed from the interaction of blood or exudates with the immediate contacting surface of the tablet, the bulk of the unused tablet easily delaminates from the seal making clean up facile. If the unused portion of the tablet is not removed from the wound site, a reservoir of hemostatic dressing stops further bleeding and to provide antimicrobial protection and healing. The tablet may be applied to any surface orientation and take any shape and thickness possible.

Claims

33-42. (canceled)

43. A hemostatic device adapted to be applied directly to a bleeding wound, comprising: a solid hemostatic tablet defining a skin contact surface and a distal side; said hemostatic tablet formed by compression of a powder of an insoluble cation exchange material and an anhydrous salt ferrate; wherein, prior to compression, said insoluble cation exchange material is comprised of beads with a portion of at least 40% of said beads being fractured; said skin contact surface applied directly to the bleeding wound while a pressure is applied to said distal side such that said skin contact surface promotes hemostasis and forms a protective seal over the bleeding wound; wherein an unused portion of the tablet separates from the seal after the seal is formed to constitute a reservoir for persistent and long lasting protection against further bleeding and exudation.

44. A hemostatic device as set forth in claim 43, further comprising: a backing layer attached to and covering a surface of said solid hemostatic tablet.

45. A hemostatic device as set forth in claim 43, further comprising: an elongated strip of flexible adhesive carrier having an adhesive surface to which said tablet is attached, said adhesive surface attachable against skin to hold said skin contact surface against the wound.

46. A hemostatic device as set forth in claim 45 wherein: a plurality of said tablets are arranged in a line along the length of said carrier, said line with said tablets capable of being aligned and held by said carrier atop an elongated open or sutured wound.

47. A hemostatic device as set forth in claim 43, further comprising: an elongated handle attached to said tablet, said tablet being in a regular or irregular three dimensional form having a uniform or varying cross section.

48. A hemostatic device as set forth in claim 43, further comprising: reinforcing fibers added to, and blended with, said mixture prior to tablet formation.

49. A hemostatic device as set forth in claim 43, further comprising: a pliable, resilient, inert carrier having an outer surface onto which a plurality of said tablets is attached, wherein said tablets are solid irregular bodies.

50. A hemostatic tablet as defined in claim 43 for use in a method of arresting the flow of blood from a bleeding wound comprising the steps of: providing the hemostatic tablet having a skin contact surface and a distal side; applying said skin contact surface directly to the bleeding wound while a pressure is applied to the distal side of the tablet such that said skin contact surface promotes blood clotting and forms a protective seal over the bleeding wound; and wherein an unused portion of the tablet separates from the seal after the seal is formed to constitute a reservoir for persistent and long lasting protection against further bleeding and exudation.

Description

BRIEF DESCRIPTION OF THE SEVERAL VIEWS OF THE DRAWING(S)

[0030] FIG. 1 is a perspective view of a one-piece tablet embodiment of the invention.

[0031] FIG. 2 is a top plan view of FIG. 1.

[0032] FIG. 3 is a side elevation view of FIG. 2.

[0033] FIG. 3A is a perspective view of a two-piece tablet embodiment of the invention.

[0034] FIG. 4 is a perspective view of an alternate embodiment of FIG. 1 showing the addition of a reinforcing foam backing.

[0035] FIG. 5 is a reverse perspective view of FIG. 4.

[0036] FIG. 6 is a section view in the direction of arrows 6-6 in FIG. 4.

[0037] FIG. 6A shows an alternate embodiment of FIG. 6.

[0038] FIGS. 7 to 10 are perspective views showing the deployment of the embodiment of FIG. 1 onto a patient's arm as an I.V. catheter is being removed.

[0039] FIG. 11 is a perspective view of another two-piece embodiment.

[0040] FIG. 12 is a top plan view of FIG. 11.

[0041] FIG. 13 is a section view of arrows 13-13 in FIG. 11.

[0042] FIG. 13A is a section view similar to FIG. 13 showing the addition of a reinforcing foam backing.

[0043] FIGS. 14 and 15 are perspective views of other one-piece tablet embodiments.

[0044] FIG. 16 is a section view in the direction of arrows 16-16 in FIG. 15.

[0045] FIGS. 17 to 24 are perspective and corresponding section views of hollow specialty configurations of the invention.

[0046] FIGS. 25 to 27C are perspective views of other configurations of one or multiple-piece embodiments affixed to an adhesive bandage.

[0047] FIGS. 28 to 33A are perspective views of other configurations of solid one-piece embodiments affixed to a delivery member.

[0048] FIG. 34 is a perspective view of another one-piece embodiment.

[0049] FIG. 35 is a section view in the direction of arrows 35-35 in FIG. 34.

[0050] FIG. 36 is a perspective view of another one-piece embodiment.

[0051] FIG. 37 is a section view in the direction of arrows 37-37 in FIG. 36.

[0052] FIGS. 37A to 37E are section views of alternate embodiments of FIG. 37.

[0053] FIGS. 38A and 38B are top plan views of smaller pellets of the invention.

[0054] FIG. 39 is a perspective view of another one-piece tablet embodiment.

[0055] FIG. 40 is a section view in the direction of arrows 40-40 in FIG. 5.

[0056] FIG. 41 is a perspective view of the embodiment of FIG. 39 packaged with an I.V. cannula inserted through the central aperture.

[0057] FIG. 42 is a perspective view of the granules of FIG. 38B stuck to the surface of a pliable wax-like shape for odd-shaped wounds.

[0058] FIG. 43 is a perspective view of the granules of FIG. 38B attached to a length of cord, string or rope.

[0059] FIG. 43A shows a plurality of the hemostatic assemblies 230 of FIG. 43 woven together to form a hemostatic mat 236.

[0060] FIG. 44 is a perspective view of a hollow wafer embodiment encasing a foam inner core.

[0061] FIG. 45 is a section view in the direction of arrows 45-45 in FIG. 44.

[0062] FIG. 46 shows a series of three separate pictorial representations of the percentage of whole beads to fragments thereof required to form the hemostatic device of this disclosure.

[0063] FIG. 47 is a pictorial view of the effect of thickness in formulating the hemostatic device of this disclosure.

[0064] FIG. 48 is a graphic display of hemostatic material density versus formation pressure.

[0065] FIG. 49 is a schematic view of a lab test set up to evaluate the ability of the solid hemostatic device versus the powderous form thereof to achieve adhesion to a blood surface.

[0066] FIG. 50 is a schematic view of an alternate lab test to that shown in FIG. 49 wherein a syringe is utilized to achieve higher static pressure in evaluating the blood adhesion characteristics of a hemostatic tablet versus a free powder hemostatic material.

[0067] FIG. 51 is a graphic representation of the hemostatic device disintegration rate versus formation pressure.

[0068] FIG. 52 is a scanning electron microscope (SEM) photo of the hemostatic device of FIG. 11 having been positioned around a vascular accessed cannula.

[0069] FIG. 53 is an enlarged view of area 53 in FIG. 52.

[0070] FIG. 54 is a SEM side elevation view of the hemostatic device having been applied atop a bleeding wound.

[0071] Exemplary embodiments are illustrated in reference figures of the drawings. It is intended that the embodiments and figures disclosed herein are to be considered to be illustrative rather than limiting.

DETAILED DESCRIPTION OF THE INVENTION

Nomenclature

[0072] 10. hemostatic device [0073] 11. hemostatic device [0074] 12. hemostatic body [0075] 13. hemostatic material [0076] 14. cannula access slot [0077] 15. skin contact surface [0078] 16. slot proximal end [0079] 17. body segment [0080] 18. slot entrance corners [0081] 19. cannula access hole [0082] 20. hemostatic assembly [0083] 21. segment opening [0084] 22. foam backing [0085] 22a. edge [0086] 23. access hole segment [0087] 24. rigid backing [0088] 25. body segment [0089] 26. cannula access slot [0090] 30. hemostatic device [0091] 32. body halves [0092] 34. mating edge [0093] 35. skin contact surface [0094] 36. catheter access hole halves [0095] 37. skin contact surface [0096] 38. slot entrance corners [0097] 39. foam backing [0098] 40. hemostatic device [0099] 42. body halves [0100] 44. fracture line [0101] 45. skin contact surface [0102] 46. groove thickness [0103] 48. skin contact surface [0104] 50. hemostatic device [0105] 52. hemostatic body [0106] 54. flat skin contact surface [0107] 56. convex skin contact surface [0108] 58. hemostatic material [0109] 60. hemostatic assembly [0110] 62. hemostatic body [0111] 63. hemostatic material [0112] 64. rigid outer backing [0113] 66. skin contact surface [0114] 68. outer surface [0115] 70. hemostatic assembly [0116] 72. hemostatic body [0117] 73. hemostatic material [0118] 74. rigid outer backing [0119] 76. skin contact surface [0120] 78. outer surface [0121] 80, 80, 80. hemostatic bandage [0122] 82, 82. adhesive carrier [0123] 84, 84. hemostatic body [0124] 85. hemostatic material [0125] 86, 86. adhesive surface [0126] 88. skin contact surface [0127] 90, 90. hemostatic bandage [0128] 92. body array [0129] 94. hemostatic body [0130] 94. body array [0131] 95, 95. hemostatic material [0132] 96. skin contact surface [0133] 97. hemostatic material [0134] 98, 98. skin contact surface [0135] 99. tear line [0136] 100, 110, 120, 130, 140, 150, 150. hemostatic device [0137] 102, 112, 122, 132, 142, 152, 152. hemostatic body [0138] 104, 114, 124, 134, 154, 154. handle [0139] 106, 116, 126, 136, 146, 156, 156. skin contact surface [0140] 108. flat end surface [0141] 118. curvilinear body end [0142] 144. flexible cord handle [0143] 148. curvilinear body end [0144] 158. curvilinear body end [0145] 160. hemostatic device [0146] 162. hemostatic body [0147] 163. hemostatic material [0148] 164, 166. convex skin contact surfaces [0149] 170. hemostatic device [0150] 172. hemostatic body [0151] 174. skin contact surface [0152] 176. fiber-filled hemostatic material [0153] 177. rigid backing [0154] 178. foam backing [0155] 180. hemostatic body [0156] 182. skin contact surface [0157] 184. hemostatic material [0158] 186. hemostatic body [0159] 188. skin contact surface [0160] 190. additive hemostatic material [0161] 192. hemostatic body [0162] 194. skin contact surface [0163] 196. hemostatic material [0164] 200. array [0165] 202. hemostatic body [0166] 204. array [0167] 206. hemostatic body [0168] 210. hemostatic device [0169] 212. hemostatic body [0170] 214. cannula access hole [0171] 216. hemostatic material [0172] 220. hemostatic assembly [0173] 222. inert carrier [0174] 224. adhesive surface [0175] 226. irregular hemostatic bodies [0176] 230. hemostatic assembly [0177] 232. string or wire [0178] 234. irregular hemostatic bodies [0179] 236. hemostatic mat [0180] 240. hemostatic assembly [0181] 242. hollow hemostatic body [0182] 244. foam insert

[0183] Broadly, the hemostatic powder composition used to form the hemostatic device of this disclosure, marketed by Biolife, L.L.C. (assignee) under the trademark STATSEAL, preferably includes an effective amount of an insoluble cation exchange material preferably combined with an effective amount of an anhydrous salt ferrate compound. Preferably, the hemostatic powder includes a mixture of the hydrogen form of a cation exchange resin (henceforth notated in short as hydrogen resin) and potassium ferrate. The hemostatic powder can be converted to a tablet by any known compression method into any size, shape, thickness and configuration. Optionally, other materials can be incorporated into the hemostatic powder to enhance performance including: antimicrobial agent, zinc oxide, binders and excipients for aiding tablet formation, magnesium stearate, sodium carboxymethylcellulose, hydroxymethyl cellulose, polyvinylpyrrolidone, medical grade fibers for added strength, natural and synthetic gums.

[0184] STATSEAL solid hemostatic devices (also referred to as tablets, discs, and wafers) are intended for use as a topical dressing for bleeding control associated with minor wounds, including control of minor external bleeding and exudates from sutures and/or surgical procedures. STATSEAL devices are preferably composed of two main components: one part potassium ferrate and seven parts hydrophilic polymer, by weight. Potassium ferrate is the oxyacid salt byproduct of the reaction between ferric acid (H.sub.2FeO.sub.4) and potassium hydroxide (KOH). Potassium fusion ferrate is manufactured by the thermal combination of iron oxide (Fe.sub.2O.sub.3) and potassium nitrate (KNO.sub.3). Potassium ferrate readily decomposes in water to produce Fe.sub.2O.sub.3 and KOH as follows:

2K.sub.2FeO.sub.4+2H.sub.2O.fwdarw.Fe.sub.2O.sub.3+4KOH+1.5 O.sub.2(g)

General

[0185] The hydrophilic polymer is a strong acid cation ion-exchange resin formed of a sulfonated copolymer of styrene and divinylbenezene (2%) in the hydrogen form. The polymer used in STATSEAL devices (PUROLITE C-122 (H); CAS No., 069011-20-7) is purchased fully hydrated and is simply heat-dried to less than 3% moisture in preparation for combination with the potassium ferrate.

[0186] STATSEAL hemostatic devices achieve their principle intended action (hemostasis) by creating a physical barrier or seal to the blood flow. The product establishes an environment in which a natural blood clot can build and form beneath the physical seal formed by STATSEAL. The hemostatic effect of the device is produced by two simultaneous modes of action: [0187] The procoagulating iron-based oxyacid salt coagulates the blood protein. [0188] The hydrophilic polymer rapidly dehydrates the blood and absorbs exudates.
The hydrophilic polymer and oxyacid salt reaction is illustrated below:

##STR00001##

[0189] As the device contacts blood, the seal begins to form immediately. The polymer quickly absorbs the liquid portion of the blood stacking the blood cells beneath. As the polymer absorbs the liquid it swells. As the cells rapidly stack beneath the tablet, they form the seal. This seal stops bleeding and also prevents further absorption of liquid by the polymer in the tablet. The swollen wetted polymer will allow the portion of the solid hemostat that is in contact with the blood to delaminate from the remaining dry material. The remaining dry tablet may be either removed or held in place with a covering dressing. A small portion of the tablet material remains attached to the surface of the blood or seal. As the wound heals beneath the seal, the remaining material falls off the wound site.

Surprising Results

[0190] Because of the reduction in surface area, high density and hardness of the solid hemostatic device, expectations were that a much longer time would be required to achieve hemostasis in a bleeding wound as compared to the free powder. Surprisingly, hemostasis was achieved in a shorter time than in the case of the free powder. Furthermore, the proximal side of the tablet developed adhesion to the bleeding wound site more rapidly than the free powder. The unexpected finding is rationalized as follows. When the solid hemostatic tablet is applied on a bleeding wound, a manual pressure applied on the distal side of the tablet imposes a very strong and uniform force on the wound surface. On the contrary, the same pressure is not easily directed on the bare powder which is scattered unevenly and is relatively thin in some areas across the wound bed, with some areas possibly with no powder coverage, resulting in lower net pressure. Consequently, the tablet adheres faster to the bleeding wound and hemostasis is achieved earlier compared to the free powder.

[0191] Another surprising finding with the tablet is the quick separation of the formed seal from the unused portion of the tablet. The seal is formed readily by the interaction of blood with the surface of the tablet in contact with the wound as discussed earlier. The quick separation between the used and unused portion of the tablet is unexpected. The seal remains intact to protect the wound while the tablet separation process is proceeding. This leaves a large reservoir of unreacted solid hemostatic material allowing persistent long term capacity to stanch further bleeding, and provide antimicrobial protection and eventual healing.

[0192] The extent of the persistent long term action can be designed by the size, shape and thickness of the tablet. The foregoing examples of size, shape and thicknesses of the tablet and limitations related therewith are intended to be illustrative and not exclusive. Moreover, the hemostatic device can be made to apply on all conceivable surfaces, including horizontal, vertical and angled surfaces. The particle size of the hemostatic powder determines, in part, the integrity of the device, particularly in the absence of a binding agent. The preferred particle size range is 80 microns to 500 microns, more preferably, 150 to 300 microns. Below 80 microns, the seal is too thin and weak while above 500 microns, the seal is not uniform and too thick with weak spots.

[0193] Any form of insoluble cation exchange material can be selected as a component of the hemostatic tablet. Preferably the cation exchange material is a cation exchange resin that is crosslinked in the range of 0.25% to 15%. The hydrogen form the cation exchange resin is preferred over other cation forms.

Embodiment Details

[0194] Referring now to the drawings, and firstly to FIGS. 1 to 3, one embodiment of the invention is there shown generally at numeral 10 and includes a circular body 12 formed of hemostatic material, the content, physical properties of which will be described herebelow. The body 12, sometimes referred to as a wafer body, a disc, or a tablet, includes an elongated cannula access slot 14 formed radially inwardly from the perimeter to the center of the body 12, terminating at a slot proximal end 16. To facilitate installation around an I.V. cannula as shown in FIGS. 7 and 8, radiused slot entrance corner 18 forming the inlet end of the cannula access slot 14 are provided.

[0195] As seen in FIG. 7, the hemostatic device 10 is positionable in the direction of arrow A so that the catheter, needle or cannula access slot 14 slides around the catheter and is positioned against the skin of the arm at the wound site W. The skin contact surface 15 of the hemostatic device 10 is then pressed against the skin in the direction of arrow C in FIG. 8 for a time sufficient for the hemostatic material of the device 10 to interact with blood and exudate from the wound site W, after which the catheter is removed in the direction of arrow B. With the hemostatic device 10 in the position shown against the skin of the arm in FIG. 9, a transparent dressing is applied thereover to protectively cover and hold the hemostatic device 10 in position over the wound site.

[0196] Referring now to FIG. 3A, an alternate embodiment of the hemostatic device is there shown at numeral 11 and includes a body segment 25 having a central cannula access hole 19 formed therethrough. The body segment 25 includes a segment opening 21 into which a wedge-shaped body 17 may be inserted in the direction of the arrow after the cannula has been placed through the slot access cannula access hole 19. An access hole segment 23 completes the cannula access hole 19 surrounding the cannula when it is properly installed.

[0197] Referring now to FIGS. 4 to 6, another embodiment of the invention is there shown at numeral 20 and includes the hemostatic device 10 of FIG. 1 adhesively attached to a matingly shaped layer of rigid backing 24 which covers one surface of the body 12. The proximal surface of the body 12 defines the skin contact surface 15.

[0198] Yet another embodiment of the invention is shown at FIG. 6A which includes the previously described hemostatic device 10 formed of a body 12, the body 12 being comprised of compressed together hemostatic material 13 as described herebelow. Foam backing 22 is provided and includes edges 22a which completely surround the otherwise exposed perimeter edges of body 12, but do not cover the skin contact surface 15.

[0199] A preferred embodiment of the invention is shown generally at numeral 30 in FIGS. 11 to 13 formed of hemostatic body halves 32 which are mateable together along proximal mating edges 34. Centrally positioned catheter access hole halves 36 are formed into the proximal edges 34 to surround the catheter when the skin contact surfaces 35 or 37 are positioned therearound against the skin. Rounded corners 38 are provided to reduce body breakage. The preferred dimensions of each of the halves 32 of this embodiment 30 are: I=0.82; w=0.44; t=0.13, slot diameter=0.12.

[0200] Referring to FIG. 13A, another embodiment of the invention which includes the hemostatic device 30 of FIG. 11, also includes a strengthening foam backing 39 adhesively attached to one surface 35 of each of the body halves 32, the skin contact surface 37 remaining free for skin attachment during installation.

[0201] In FIG. 14, another embodiment of the hemostatic device is there shown at 40 and includes body halves 42 which are connected along fracture line 44 and held together by a groove thickness 46 of hemostatic material. The purpose of this embodiment 40 is to facilitate fracture of the body halves 42 along the fracture line 44 to be easily broken to accommodate better skin surface contact in an area of curved skin surfaces.

[0202] In FIGS. 15 and 16, the hemostatic device 50 formed of a body 52 having a flat skin contact surface 52 and a convex skin contact surface 56 is provided.

[0203] Referring now to FIGS. 17 to 24, a series of hollow specialty configurations of the invention are there shown. Each of these hemostatic assemblies 60 and 70 provide a concave curvilinear skin contact surface 66 and 76, respectively, formed of a cup or thimble-shaped hemostatic body 62 and 72, respectively. To add strength to each of these hemostatic assemblies 60 and 70, a rigid or semi-rigid outer backing 64 and 74, respectively, having a smooth protective outer surface 68 and 78, respectively, are provided. A particular use embodiment may be for a bleeding fingertip or toenail of a dog when trimmed too short.

[0204] Then, in FIGS. 21 to 24, convex or spherically-shaped outer skin contact surface 66 and 76 of cup or thimble-shaped hemostatic bodies 60 and 70, respectively, are provided. These hemostatic bodies 62 and 72 are supported on their inner surfaces by adhesive attachment to a rigid or semi-rigid mating outer backing 64 or 74, respectively.

[0205] Referring now to FIGS. 25 to 27C, a series of hemostatic bandages 80, 80, 90, and 90 are there shown. Each of these hemostatic bandages include an elongated strip of flexible adhesive carrier 82 having an adhesive surface 86 thereon. In embodiment 80, a circular tablet-shaped body 84 formed of hemostatic material 85 and having a skin contact surface 88 is centrally positioned and adhesively attached to the adhesive carrier 82. The hemostatic bandage 90 includes a rectangular-shaped body 94 formed of compressed together hemostatic material 95 as described herebelow and also having a skin contact surface 98.

[0206] With respect to the hemostatic bandage 90 in FIG. 27A, an array 94 of thin, smaller hemostatic bodies are attached to the adhesive surface 86, each of which are formed of hemostatic material 95 and having a skin contact surface 98. This embodiment 90 provides for flexibility of the skin contact surfaces 98 over an irregularly or curve-shaped skin surface. Likewise, the embodiment 80 in FIG. 27B includes a body array 92 of thin, small hexagonally-shaped hemostatic bodies, each of which is formed of hemostatic material 97 and having a skin contact surface 96. This body array 92 provides alternative ability to conform to curved and irregular skin surfaces.

[0207] In FIG. 27C, embodiment 80 provides the adhesive carrier 82 having spaced transverse tear or cut lines 98 to easily adjust the length of the adhesive carrier 82. A row of very small closely spaced hemostatic bodies 84, adhesively attached to adhesive surface 86 and extending lengthwise along the flexible adhesive carrier 82, are alignable over an elongated wound, for example, a sutured wound. The individual hemostatic bodies provide great flexible adaptability over a contoured skin surface.

[0208] Referring to FIGS. 28 to 33A, an array of a plurality of hemostatic devices 100, 110, 120, 130, 140, 150 and 150 are there shown, each having a solid uniquely configured hemostatic body 102, 112, 122, 132, 142, 152 and 152 providing skin contact surfaces 106, 116, 126, 136, 146, 156 and 156 attached to an elongated handle 104, 114, 124, 134, 144, 154 and 154. Each of the configurations of the solid hemostatic bodies may be adapted to deal with bleeding wounds at various body sites. The flexible cord handle 144 of embodiment 140 provides an additional adaptation for replacement and withdrawal of the hemostatic body 142, while the curved handle 154 facilitates manipulation and positioning of the contoured irregular hemostatic body 152.

[0209] Referring now to FIGS. 34 and 35, still another hemostatic device 160 is there shown formed of a body 162 having outwardly extending curvilinear skin contact surfaces 164 and 166. These surfaces 164 and 166 may be identical or may be of differing curvature to enhance versatility in the application of this embodiment 160. The body 162 is formed of hemostatic material 163 as described herebelow.

[0210] Referring now to FIGS. 36 and 37, another one-piece embodiment of the invention is there shown generally at numeral 170 having reinforcing fibers blended with the hemostatic material 176 prior to the body 172 being pressure formed. Opposing skin contact surfaces 174 are provided. Then, in FIG. 37A, the reinforced hemostatic material 176 of body 172 is further reinforced by a screen backing 177 adhesively attached to one of the skin contact surfaces 174. In FIG. 37B, the body 172 is reinforced by a thicker reinforcing foam backing 178, while in FIG. 37C, the body 180 is formed having a mesh material blended with the hemostatic material 184. In FIG. 37D, a very open foam filled rigid or semi-rigid hemostatic powder 190 is utilized to form the hemostatic body 186. Lastly, in FIG. 37E, various additives may be blended with the hemostatic material 196 to form the hemostatic body 192 having skin contact surfaces 194. Note that the additives 196 blended with the hemostatic material may be in various forms, including binding additives, lubricants and antimicrobials.

[0211] In FIGS. 38A and 38B, arrays 200 and 204 of miniature solid hemostatic bodies 202 and 206 are provided which are compression formed of the powderous hydrostatic material, but, although smaller in size, nonetheless reduce the mess associated with the loose granular hydrostatic powder material. Hemostatic bodies 202 and 206 may be in a form and size similar to KITTY LITTER which, again, reduce the messiness associated with the powderous hemostatic material used to press form these hemostatic bodies 202 and 206.

[0212] Referring now to FIGS. 39, 40 and 41, a completely circular tablet-shaped hemostatic device 210 formed of an annular-shaped hemostatic body 212 is there provided. A central hole 214 is formed there through sized to receive the cannula of a catheter slidably inserted therethrough and which may be packaged as shown in FIG. 41 ready for use.

[0213] In FIG. 42, a plurality of small solid hemostatic irregular bodies 226 are attached to a pliable, resilient inert carrier 222 having an adhesive surface 224 to form the hemostatic assembly 220 there shown. This embodiment 220 facilitates applying pressure of the hemostatic bodies 226 against various irregular skin surfaces. FIG. 43 shows an embodiment 230 of irregular hemostatic bodies 234 which have been strung along the length of a string or wire 232. Then, in FIG. 43A, a plurality of these hemostatic assemblies 230 may be woven together to form a hemostatic mat 236.

[0214] In FIGS. 44 and 45, to reduce the volume of compressed hemostatic material, a hollow hemostatic body 242 encasing a foam insert 244 form the hemostatic assembly 240.

Example 1

Formation Pressure

[0215] The hemostatic composition for the powder is preferably 1:7 weight mixture of ferrate: hydrogen resin, although this ratio has a range of 1:3 to 1:12, The hydrogen resin is, preferably, the hydrogen form of the 2% crosslinked, sulfonated poly(styrene) resin. The hydrogen resin is available in whole insoluble beads in the range of 500 microns or can be ground into much finer fragments averaging in size from 80 microns to 200 microns. Device formation is based, in part, on the percent of resin fractured to whole beads. The crosslinked hydrogen ion exchange resin will not melt as temperature is increased nor will it cold flow with pressure. Therefore whole resin beads alone cannot be formed into a tablet with pressure.

[0216] As seen in FIG. 46, column 3, at 45k psi, whole beads will not bind together into a solid. As shown in column 3 in FIG. 46, mixtures of whole beads and fragments (61 to 89%:39 to 11%) will bind together. A sufficient percentage of fragments to whole beads (40 to 100%:0 to 60%) as shown in column 1 are required to form a usable solid by filling voids created by stacking the whole beads to allow sufficient interaction for mechanically binding the material together into a tablet.

[0217] All or some portion of the fragments may be resin alone or may be replaced with other additives to fill the voids between the whole resin beads. Those additives may be one or a combination of: potassium ferrate (preferred), binders (stearates, waxes), solid lubricants, microbial agents, other amorphous solid materials (calcium carbonate), other non-spherical absorbent materials that are dissimilar in size to the resin, to increase the packing density and contact surfaces to allow a strong tablet to be formed.

Example 2

Minimum Thickness

[0218] As seen in FIG. 47, the hemostatic powder preferably of 1:7 potassium ferrate: hydrogen resin, was made into solid bodies in tablet form using a lab press. Preliminary tablet formation testing of tablet thicknesses from about 0.5 mm to 30 mm established a minimum thickness of about 0.5 mm for compressing the hemostatic powder into a solid device. The photos in FIG. 47 indicate that at least 0.5 mm thickness is needed to create a complete usable tablet. The material was ground to <250 m. However, changing the grind size may affect the minimum thickness of powder needed to create a complete tablet. Based on handling or usability, the thin (0.53 mm) 20 mm diameter tablet created with 45K psi (#3) had more integrity than did the thin tablet at 29K psi formation pressure. In Test #1, 29K psi was not sufficient to form a 0.426mm thick tablet, but in Test #2, a fragile and unstable tablet having a thickness of 0.535 mm was formed.

[0219] Three tests were used for the evaluation of a usable hemostatic device for application: Density Test, Formation Test, and Friability Test.

Example 3

Density Test

[0220] In FIG. 48, a Tablet Density Test was used to determine the relationship of solid density (ml/g) to formation pressure (psi), from 8K to 45K psi. Above 45K psi, the density increase appears to flatten with respect to press pressure. The pressure of 45K psi is the maximum pressure rating for the 20 mm round table die used for testing, to determine the amount of force needed to form a solid tablet. The tablet integrity was determined by measuring harness and wetting rate. In addition, manual breakage of multiple tablets was also used in selecting the appropriate tablet parameters.

[0221] Tests on the lab press, a single LANE STOKES disc press, using a thick 20 mm round die (0.487 in.sup.2) showed that: [0222] below 8K psi the tablets are too fragile to handle and often break while being removed from the die; [0223] between 12K and 15K psi, the tablets could be handled but break easily; [0224] at between 20L and 33K psi, the tablets are acceptable; further evaluation was performed at 29K psi.

Example 4

Friability Test

[0225] The Tablet Friability Test is based on the following FDA Guidance for tablets: [0226] Q4B Evaluation and Recommendation of Pharmacopoeial Texts for Use in the ICH Regions: Annex 9 Disc Friability General Chapter [0227] http://www.fda.gov/downloads/Drugs/GuidanceComplianceRegulatoryInformation/Guidances/UMC176888.pdf

[0228] Friability is a determination of mass loss during a tumbling test. A tablet is dropped 100 times from a specific height and measurement is taken to determine how much mass is lost. The mean loss should be no more than 1% for tablets, per USP, unless otherwise specified by dosier.

[0229] The USP tests ensure that tablets packed in bottle with many other tablets do not lose mass prior to being ingested by the patient. A mass loss would result in a reduction of medication being ingested. In the case of the a topically applied hemostatic tablet there is no prescribed medication and, more importantly the tablets will be packaged as individual units and protected to ensure the tablets are intact on arrival. The risk of any breakage will be mitigated via packaging.

[0230] A modified Tablet Friability Test was designed by pouring tablets through a 2 PVC tube from a beaker into a catch beaker. The height from the top of the PVC to the surface of the catch beaker was set at 150 mm (based on the USP Friability Protocol).

[0231] The Tablet Friability Test showed that the average loss was 2.5%. This amount of loss is acceptable because the tablet is externally/topically applied to the wound surface and, breakage is mitigated through unitized protected packaging.

Example 5

Adhesion Test

[0232] The 20 mm diameter tablet and the free powder prepared from the same composition consisting of 1:7 potassium ferrate: hydrogen resin, were tested for in terms of their ability to achieve adhesion to the blood surface. A blood seal test was employed as follows: [0233] 1. 0.10 mL of EDTA stabilized porcine blood was placed and spread evenly in the one inch diameter circle outlined in a plastic boat; [0234] 2. The test material was poured or placed on the top of the evenly spread blood; [0235] 3. Moderate manual pressure was placed on top of the test material for 90 seconds; [0236] 4. Using a spatula, the blood seal formed by action of blood and the test material was tested for adhesion and strength by scrapping with a spatula.

[0237] The results showed that the free powder created an uneven blood seal with moderate adhesion and upon scrapping, provided moderate strength in terms of the lifted seal. The excess portion of the unused free powder had been exposed to and deactivated in the atmosphere and has lost most of its capacity for further use. On the other hand, the 20 mm diameter tablet broke open into two parts, the first part revealed a thicker blood seal with excellent adhesion and strength and, the second part having a significant portion of the tablet unused and intact. The second portion constituting the used tablet remains as a reservoir to stop bleeding and absorption of exudates.

Example 6

Hemostasis Comparison Powder vs. Solid Tablet

[0238] Referring to FIG. 49, the 20 mm diameter tablet and the free powder prepared from the same composition consisting of 1:7 potassium ferrate: hydrogen resin were tested for hemostasis efficacy using a low pressure gravity flow system. The results showed that for a low pressure gravity flow system, there were no impact on hemostasis efficacy by mechanically compressing the powder versus using the powder itself. In the next example, testing at high pneumatic pressure distinctly demonstrate that the tablet surprisingly outperforms the free powder.

[0239] A 60 ml syringe is filled with approximately 25 ml of blood. The test block formed from a 1.5 clear acrylic block. Assuming the entry hole designed to fit a barbed fitting to connect to flexible vinyl tubing and a diameter outlet hole. The syringe is elevated to 30 cm above the top of the test block, creating a pressure of 30 cm water which equated to 20 mm Hg (mercury).

[0240] The valve was opened and the blood was allowed to surface. The valve was closed and the blood was spread over an area approximately 0.5 from the outlet. The test material was placed over the blood covering the outlet hole. Contact pressure was held with a 100 gram mass for 60 seconds. After the 60 seconds the 100 gram mass was removed and the valve was opened for 30 seconds. If no blood exits the hole sealing of the hole occurred and the test sample passed the test.

[0241] As shown in Table 1 below, both the powder (N=5) and the Tablet (Tablet) (N=10) passed all testing.

TABLE-US-00001 TABLE 1 Hemostasis comparison powder to tablet Powder Solid Tablet 1 Pass Pass 2 Pass Pass 3 Pass Pass 4 Pass Pass 5 Pass Pass 6 Pass 7 Pass 8 Pass 9 Pass 10 Pass

Example 7

Sealing Test

Powder vs. Solid Tablet

[0242] The 20 mm diameter tablet and the free powder prepared from the same composition consisting of 1:7 potassium ferrate: hydrogen resin, were tested for hemostasis efficacy using a high pneumatic pressure system as detailed below in the study design and experiment. The apparatus is schematically represented in FIG. 50. The results indicated that the tablet was unexpectedly superior to the free powder in hemostasis efficacy during high pneumatic pressure testing. The tablet creates a significantly stronger seal capable of stopping higher pressure bleeding than the free powder that defies expectation. This surprising finding implies that the uniform surface of the tablet enables a much greater manual pressure to be exerted on the blood than the free powder which provides a non-uniform and irreproducible force on the blood. Furthermore, the dense nature of the tablet surface in contact with the blood and the huge reservoir of the composition concentrated in the tablet enable rapid dehydration and significantly better adhesion than for the loose and low density powder. The much greater surface area of the loose powder would lead to the expectation that the powder would perform significantly better than the tablet where less surface is in contact with the blood.

[0243] In this test, a test block is created from a 1.5 clear acrylic block. The test block has an entry hole designed to fit a barbed fitting to connect to flexible vinyl tubing and a diameter outlet hole. The first step is to pull back the syringe plunger, power up the manometer and set the manometer to record the maximum value. The syringe plunger is compressed to pressurize the system until the blood seal fails. The manometer records the maximum pressure created just prior to the seal failure. Next blood is placed around the outlet hole. The tablet is then placed over the blood. Care is taken to ensure that the blood completely encircles the hole, and that the tablet completely covers the hole as well. A gloved finger is used to apply slight manual pressure to the tablet. The pressure forces the liquid blood from beneath the tablet. The tablet is allowed to set for 15 seconds and then the plunger is compressed.

[0244] During the first attempt, the maximum reading on the manometer reached 408 mm Hg and the tubing dislodged from the syringe. A zip tie was used to prevent future failures, and a pressure of 500 mm Hg was set at an end point.

[0245] The tablet was tested 15 times and all consistently reached the end point of 500 mm Hg without failure of the seal. In contrast, the free powder only reached an end point of 100 mm Hg demonstrating the superior and unexpected performance of the tablet.

[0246] Comparatively loose powder reached an average hold pressure of 310 mm Hg in the same test. A small foil disk was used to prevent the powder from filling and occluding the hold in the loose powder testing. The powder also required a 75 g mass to maintain the seal integrity. Surprisingly the solid preformed better than did the loose powder with no addition mass holding the solid in place above the simulated wound.

Example 8

Oxygen Generation

[0247] Upon wetting potassium ferrate decomposes. Upon decomposition potassium ferrate released oxygen gas:

2K.sub.2FeO.sub.4+2H.sub.2O.fwdarw.Fe.sub.2O.sub.3+4KOH+1.5 O.sub.2(g)

[0248] A test is designed to measure the amount of oxygen generated by a mass of PRO QR powder vs. a similar mass of powder compressed into a solid tablet upon wetting. For this test 45K psi was applied to 2-3 grams of powder in a 20 mm diameter tablet die using a lab press. In manufacturing typically 29K psi will be required to produce a 20 mm diameter tablet. This test is using excessive force to further exacerbate any potential for decomposition of potassium ferrate due to mechanical compression of the powder.

[0249] This test concluded that upon wetting powder will liberate 3.90 ml of oxygen gas per gram of powder, and powder compressed into a tablet will liberate 4.05 ml of oxygen gas per gram of powder. The percent difference between the oxygen collected in the test for the powder vs. the tablet is 3.77%. This difference is with the 5% coefficient of variance which is used to indicate a good analytical test. Therefore the results are nearly equal and it can be concluded compressing the powder into a tablet does not cause degradation of the potassium ferrate.

[0250] In this experiment, a sample of the powder or tablet is placed in a small dry bottle. The bottle is sealed creating a closed system where any gas generated is forced to exit thru a small tube. This outlet of the exit tube is set up to bubble gas into a partially submerged inverted filled graduated cylinder (filled with water). As the gas bubbles into the graduated cylinder it displaces an equal volume of water. This allows for the evolved gas to be measured.

[0251] As the powder or tablet is wetted, the potassium ferrate decomposed releasing oxygen. The test material is placed in the dry bottle in the closed system. A syringe is used to inject water into the bottle. In this test, 15 ml of water was injected each time. This volume of water was accounted for in the calculations. Also the graduated cylinder was replaced with a 50 ml burette for more accurate reading of the results. The starting point for the gas measurements was the displacement point created by injecting 15 ml of water into the empty bottle in the closed system.

Example 9

Disc Disintegration Test

[0252] This test is designed to determine the time for the hemostatic tablet to physically break down into the components in water. The tablet is composed of manually compressed powder composed of a hydrophilic polymer that swells as it absorbs water and potassium ferrate. As the polymer wets and swells it causes disintegration of the tablet. This wetting rate is dependent upon the pressure at which the tablet is pressed.

[0253] In this experiment, water is flowed across the tablet in a tube. A screen with approximately 2 mm openings is used to support the tablet in a 2.9 cm diameter tube. A siphon break is elevated to maintain a liquid level 2-3 inches above the screen. The flow rate for the test was 562 ml/min. The end point is when there is no longer any material above the screen.

[0254] The pump is turned on. The disc is dropped into the tube with the water running and a stopwatch is started. The disc is observed and, when there is no longer any material above the screen the time recorded.

[0255] Nine (9) tablets were produced on a lab press using a 20 mm die and varying amount of force, The machine made sample was produced on a Stokes single lane tablet press. That machine made samples of average weight of 1,500 mg for the Lab Press. Fifteen (15) samples were produced on the Stokes single lane disc press. Average Mass of 750 mg. All tablets tested had a similar thickness of near .

[0256] Disintegration rate is shown to be linear with respect to press pressure for tablets between 8K (disintegration time: 40 seconds) and 45K psi (disintegration time: 180 seconds) for a 20 mm diameter round tablet. Therefore, wetting or disintegration rate is a relationship of the closeness of particles and capillary action to wet the next layer of material and minimum preferred disintegration time of 40 seconds is achieved at 8K psi formation pressure.

[0257] While a number of exemplary aspects and embodiments have been discussed above, those of skill in the art will recognize certain modifications, permutations and additions and subcombinations thereof. It is therefore intended that the following appended claims and claims hereinafter introduced are interpreted to include all such modifications, permutations, additions and subcombinations that are within their true spirit and scope.