Apparatus for aspirating, irrigating and cleansing wounds

Abstract

An apparatus for cleansing wounds in which irrigant fluid from a reservoir connected to a conformable wound dressing and wound exudate from the dressing are recirculated by a device for moving fluid through a flow path which passes through the dressing and a means for fluid cleansing and back to the dressing. The cleansing means (which may be a single-phase, e.g. microfiltration, system or a two-phase, e.g. dialytic system) removes materials deleterious to wound healing, and the cleansed fluid, still containing materials that are beneficial in promoting wound healing, is returned to the wound bed. The dressing and a method of treatment using the apparatus.

Claims

1. An apparatus for treatment of a wound, comprising: a lower porous film comprising a plurality of apertures, the lower porous film adapted to conform to a shape of the wound, wherein the lower porous film comprises a disc-shaped periphery; and a plurality of circumferentially-arranged spaces, each space defined by the lower porous film and an upper membrane attached to the lower porous film, wherein each space has an outer periphery adjacent the disc-shaped periphery of the lower porous film and opens in a radially-inward direction toward a center portion of the lower film, and wherein the outer peripheries of each of the plurality of circumferentially-arranged spaces are circumferentially spaced apart around the disc-shaped periphery of the lower porous film; wherein the lower porous film is sealed to said upper membrane along at least a portion of the outer peripheries of each of the plurality of the circumferentially-arranged spaces.

2. The apparatus of claim 1, further comprising a backing layer capable of forming a relatively fluid tight seal of closure over the wound.

3. The apparatus of claim 2, further comprising a conduit configured to be in fluid communication with a space under the backing layer.

4. The apparatus of claim 2, further comprising a wound filler positionable beneath the backing layer and above the lower porous film.

5. The apparatus of claim 4, wherein the wound filler is conformable to the shape of the wound.

6. The apparatus of claim 2, further comprising a source of negative pressure configured to provide negative pressure to a space beneath the backing layer.

7. The apparatus of claim 1, wherein each of the outer peripheries of the plurality of circumferentially-arranged spaces has a curved shape.

8. The apparatus of claim 1, wherein each of the outer peripheries of the plurality of circumferentially-arranged are separated by portions comprising only the lower porous film.

9. The apparatus of claim 1, comprising four circumferentially-arranged spaces.

10. The apparatus of claim 1, comprising six circumferentially-arranged spaces.

11. The apparatus of claim 1, comprising eight circumferentially-arranged spaces.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

(1) The present invention will now be described by way of example only with reference to the accompanying drawings in which:

(2) FIG. 1 is a schematic view of an apparatus for aspirating, irrigating and/or cleansing a wound according to the first aspect of the present invention.

(3) It has a single-phase system means for fluid cleansing in the form of an ultrafiltration unit.

(4) FIG. 2 is a schematic view of an apparatus for aspirating, irrigating and/or cleansing a wound according to the first aspect of the present invention.

(5) It has a two-phase system means for fluid cleansing in the form of a dialysis unit, or a biphasic extraction unit.

(6) FIGS. 3a-b, 4a-b, 5a-b, 6a-b, and 7a-b are cross-sectional views of conformable wound dressings, of the second aspect of the present invention for aspirating and/or irrigating wounds.

(7) In these, FIGS. 3a to 7a are cross-sectional plan views of the wound dressings, and FIGS. 3b to 7b are cross-sectional side views of the wound dressings.

(8) FIGS. 8a-d, 9a-b, and 10a-c are various views of inlet and outlet manifold layouts for the wound dressings of the second aspect of the present invention for respectively delivering fluid to, and collecting fluid from, the wound.

(9) FIG. 11 is a schematic view of an apparatus for aspirating, irrigating and/or cleansing a wound according to the first aspect of the present invention.

(10) It has a single-phase system means for fluid cleansing in the form of an ultrafiltration unit.

(11) FIG. 12 is a schematic view of an apparatus for aspirating, irrigating and/or cleansing a wound according to the first aspect of the present invention.

(12) It has a two-phase system means for fluid cleansing in the form of a dialysis unit, or a biphasic extraction unit.

(13) FIGS. 13a-b, 14, 15, 16a-b, 17, 18a-b, and 19 to 26 are cross-sectional views of conformable wound dressings, of the second aspect of the present invention for aspirating and/or irrigating wounds.

(14) FIG. 27 is a schematic view of another apparatus for aspirating, irrigating and/or cleansing a wound according to the first aspect of the present invention.

(15) It has a single-phase system means for fluid cleansing in the form of an ultrafiltration unit.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT

(16) Referring to FIG. 1, the apparatus (1) for aspirating, irrigating and/or cleansing wounds comprises a conformable wound dressing (2), having a backing layer (3) which is capable of forming a relatively fluid-tight seal or closure (4) over a wound (5) and one inlet pipe (6) for connection to a fluid supply tube (7), which passes through the wound-facing face of the backing layer (5) at (8), and one outlet pipe (9) for connection to a fluid offtake tube (10), which passes through the wound-facing face at (11), the points (8), (11) at which the inlet pipe and the outlet pipe passes through and/or under the wound-facing face forming a relatively fluid-tight seal or closure over the wound, the inlet pipe being connected via means for flow switching between supply and recirculation, here a T-valve (14), by the fluid supply tube (7) to a fluid reservoir (12) and to a fluid recirculation tube (13) having a means for bleeding the tube, here a bleed T-valve (16) to waste, e.g. to a collection bag (not shown), the outlet pipe (9) being connected to a fluid offtake tube (10), connected in turn to means for fluid cleansing (17), here in the form of an ultrafiltration unit, connected to the inlet pipe (6) via the fluid recirculation tube (13) and T-valve (14), and a device for moving fluid through the wound and means for fluid cleansing (17), here a peristaltic pump (18), e.g. preferably a small portable peristaltic pump, acting on the fluid circulation tube (13) with the peripheral rollers on its rotor (not shown) to apply a low negative pressure on the wound.

(17) The ultrafiltration unit (17) is a single-phase system. In this the circulating fluid from the wound and the fluid reservoir passes through a self-contained system in which materials deleterious to wound healing are removed and the cleansed fluid, still containing materials that are beneficial in promoting wound healing, is returned via the recirculation tube to the wound bed.

(18) (In a variant of this apparatus, there are two inlet pipes (6), which are connected respectively to a fluid supply tube (7) and fluid recirculation tube (13), respectively having a first valve (19) for admitting fluid into the wound from the fluid reservoir (12) and a second valve (20) for admitting fluid into the wound from the recirculation tube.

(19) Usually in use of the apparatus, when the first valve (19) is open, the second valve (20) is shut, and vice versa.)

(20) In use of the apparatus (1), the valve (16) is opened to a collection bag (not shown), and the T-valve (14) is turned to admit fluid from the fluid reservoir to the wound dressing through the fluid supply tube (7) and inlet pipe (6). (In the variant of this apparatus having two inlet pipes (6), which are connected respectively to a fluid supply tube (7) and fluid recirculation tube (13), the first valve (19) for admitting fluid into the wound from the fluid reservoir (12) is opened and the second valve (20) is shut, and vice versa.)

(21) The pump (18) is started to nip the fluid recirculation tube (13) with the peripheral rollers on its rotor (not shown) to apply a low positive pressure on the wound. It is allowed to run until the apparatus is primed throughout the whole length of the apparatus flow path and excess fluid is voided to waste via the bleed T-valve (16) into the collection bag (not shown).

(22) The T-valve (14) is then turned to switch from supply and recirculation, i.e. is set to close the wound to the fluid reservoir (12) but to admit fluid into the wound from the fluid recirculation tube (13), and the bleed T-valve (16) is simultaneously closed.

(23) (In the variant of this apparatus, where there are two inlet pipes (6), which are connected respectively to a fluid supply tube (7) and fluid recirculation tube (13), the first valve (19) is closed and a recirculating system set up by opening the second valve (20) for admitting fluid into the wound from the recirculation tube (13).

(24) The circulating fluid from the wound and the fluid reservoir (12) passes through the ultrafiltration unit (17). Materials deleterious to wound healing are removed and the cleansed fluid, still containing materials that are beneficial in promoting wound healing, is returned via the recirculation tube (13) to the wound bed.

(25) The recirculation of fluid may be continued as long as desired.

(26) Switching between supply and recirculation is then reversed, by turning the T-valve (14) to admit fluid from the fluid reservoir to the wound dressing through the fluid supply tube (7) and inlet pipe (6).

(27) (In the variant of this apparatus having two inlet pipes (6), which are connected respectively to a fluid supply tube (7) and fluid recirculation tube (13), the first valve (19) for admitting fluid into the wound from the fluid reservoir (12) is opened and the second valve (20) is shut, and vice versa.)

(28) The bleed valve (16) is simultaneously opened, so that fresh fluid flushes the recirculating system.

(29) The running of the pump (18) may be continued until the apparatus is flushed, when it and the fluid recirculation is stopped.

(30) If, e.g. the wound is in a highly exuding state, there is a positive change in the balance of fluid in recirculation. It may be necessary to bleed fluid from recirculation, by opening the bleed T-valve (16) to bleed fluid from the recirculation tube (13).

(31) Referring to FIG. 2, the apparatus (21) is a variant of that of FIG. 1, with identical, and identically numbered, components, except for the means for fluid cleansing, which is in the form of a two-phase system, here a dialysis unit (23).

(32) In this, there is one system through which the circulating fluid from the wound and the fluid reservoir passes and from which deleterious materials are removed by selectively permeable contact with a second system, through which passes a cleansing fluid.

(33) The dialysis unit (23) thus has an internal polymer film, sheet or membrane (24), selectively permeable to materials deleterious to wound healing, which divides it into a) a first chamber (25), through which passes a cleansing fluid across one surface of the polymer film, sheet or membrane, and b) a second chamber (26), through which passes the circulating fluid from the wound and the fluid reservoir (12), and from which deleterious materials are removed

(34) The dialysis unit (23) thus has a dialysate inlet pipe (28) connecting to a dialysate supply tube (29) which passes to a peristaltic pump (38), e.g. preferably a small portable peristaltic pump, acting on the dialysate supply tube (29) with the peripheral rollers on its rotor (not shown) to supply cleansing fluid across the surface of the polymer film, sheet or membrane (28) in the first chamber (25) from a dialysate reservoir (not shown) via a valve (34).

(35) The dialysis unit (23) also has a dialysate outlet pipe (30) connecting to a dialysate outlet tube (31) which passes to waste via a second bleed T-valve (36) into, e.g. a collection bag (not shown).

(36) Operation of this apparatus is similar to that of FIG. 1, except for the dialysis unit (23), in that at some point after the irrigation system is primed and steady state recirculation established through the length of the apparatus flow path, the valve (34) and second bleed valve (36) are opened.

(37) The pump (38) is started to nip fluid dialysate tube (29) with the peripheral rollers on its rotor (not shown) to pump cleansing fluid to the first chamber from a dialysate reservoir (not shown) and out to waste via the bleed valve (36) into the collection bag (not shown).

(38) The dialysis unit (23) is a module (or scrubbing cartridge) with a substrate that changes colour to indicate the presence of detrimental factors in the cleansed fluid, and that the scrubbing cartridge is exhausted and should be renewed.

(39) Referring to FIGS. 3a-b to 6a-b, each dressing (41) is in the form of a conformable body defined by a microbe-impermeable film backing layer (42) with a uniform thickness of 25 micron, with a wound-facing face (43) which is capable of forming a relatively fluid-tight seal or closure over a wound.

(40) The backing layer (42) extends in use on a wound over the skin around the wound. On the proximal face of the backing layer (43) on the overlap (44), it bears an adhesive film (45), to attach it to the skin sufficiently to hold the wound dressing in place in a fluid-tight seal around the periphery of the wound-facing face (43) of the wound dressing.

(41) There is one inlet pipe (46) for connection to a fluid supply tube (not shown), which passes through and/or under the wound-facing face (43), and one outlet pipe (47) for connection to a fluid offtake tube (not shown), which passes through and/or under the wound-facing face (43).

(42) Referring to FIGS. 3a and 3b, one form of the dressing is provided with a wound filler (48) under a circular backing layer (42).

(43) This comprises a generally frustroconical, toroidal conformable hollow body, defined by a membrane (49) which is filled with a fluid, here air or nitrogen, that urges it to the wound shape.

(44) The filler (48) may be permanently attached to the backing layer with an adhesive film (not shown) or by heat-sealing.

(45) The inlet pipe (46) and outlet pipe (47) are mounted centrally in the backing layer (42) above the central tunnel (50) of the toroidal hollow body (48) and each passes through the backing layer (42), and each extends in pipes (51) and (52) respectively through the tunnel (50) of the toroidal hollow body (48) and then radially in diametrically opposite directions under the body (48).

(46) This form of the dressing is a more suitable layout for deeper wounds.

(47) Referring to FIGS. 4a and 4b, a more suitable form for shallower wounds is shown. This comprises a circular backing layer (42) and a circular upwardly dished first membrane (61) with apertures (62) that is permanently attached to the backing layer (42) by heat-sealing to form a circular pouch (63).

(48) The pouch (63) communicates with the inlet pipe (46) through a hole (64), and thus effectively forms an inlet pipe manifold that delivers the circulating fluid directly to the wound when the dressing is in use.

(49) An annular second membrane (65) with openings (66) is permanently attached to the backing layer (42) by heat-sealing to form an annular chamber (67) with the layer (42).

(50) The chamber (67) communicates with the outlet pipe (47) through an orifice (68), and thus effectively forms an outlet pipe manifold that collects the fluid directly from the wound when the dressing is in use.

(51) Referring to FIGS. 5a and 5b, a variant of the dressing of FIGS. 4a and 4b that is a more suitable form for deeper wounds is shown.

(52) This comprises a circular backing layer (42) and a filler (69), in the form of an inverted frustroconical, solid integer, here a resilient elastomeric foam, formed of a thermoplastic, or preferably a cross-linked plastics foam.

(53) It may be permanently attached to the backing layer (42), with an adhesive film (not shown) or by heat-sealing.

(54) A circular upwardly dished sheet (70) lies under and conforms to, but is a separate structure, permanently unattached to, the backing layer (42) and the solid integer (69).

(55) A circular upwardly dished first membrane (71) with apertures (72) is permanently attached to the sheet (70) by heat-sealing to form a circular pouch (73) with the sheet (70).

(56) The pouch (73) communicates with the inlet pipe (46) through a hole (74), and thus effectively forms an inlet pipe manifold that delivers the circulating fluid directly to the wound when the dressing is in use.

(57) An annular second membrane (75) with openings (76) is permanently attached to the sheet (70) by heat-sealing to form an annular chamber (77) with the sheet (70).

(58) The chamber (77) communicates with the outlet pipe (47) through an orifice (78), and thus effectively forms an outlet pipe manifold that collects the fluid directly from the wound when the dressing is in use.

(59) Alternatively, where appropriate the dressing may be provided in a form in which the circular upwardly dished sheet (70) functions as the backing layer and the solid filler (69) sits on the sheet (70) as the backing layer, rather than under it. The filler (69) is held in place with an adhesive film or tape, instead of the backing layer (42).

(60) Referring to FIGS. 6a and 6b, a dressing that is a more suitable form for deeper wounds is shown.

(61) This comprises a circular backing layer (42) and a filler (79), in the form of an inverted generally hemispherical integer, here a resilient elastomeric foam or a hollow body filled with a fluid, here a gel that urges it to the wound shape, and permanently attached to the backing layer with an adhesive film (not shown) or by heat-sealing.

(62) The inlet pipe (46) and outlet pipe (47) are mounted peripherally in the backing layer (42).

(63) A circular upwardly dished sheet (80) lies under and conforms to, but is a separate structure, permanently unattached to, the backing layer (42) and the filler (79).

(64) A circular upwardly dished bilaminate membrane (81) has a closed channel (82) between its laminar components, with perforations (83) along its length on the outer surface (84) of the dish formed by the membrane (81) and an opening (85) at the outer end of its spiral helix, through which the channel (82) communicates with the inlet pipe (46), and thus effectively forms an inlet pipe manifold that delivers the circulating fluid directly to the wound when the dressing is in use.

(65) The membrane (81) also has apertures (86) between and along the length of the turns of the channel (82).

(66) The inner surface (87) of the dish formed by the membrane (81) is permanently attached at its innermost points (88) with an adhesive film (not shown) or by heat-sealing to the sheet (80). This defines a mating closed spirohelical conduit (89).

(67) At the outermost end of its spiral helix, the conduit (89) communicates through an opening (90) with the outlet pipe (47) and is thus effectively an outlet manifold to collect the fluid directly from the wound via the apertures (86).

(68) Referring to FIGS. 7a and 7b, one form of the dressing is provided with a circular backing layer (42). A first (larger) inverted hemispherical membrane (92) is permanently attached centrally to the layer (42) by heat-sealing to form a hemispherical chamber (94) with the layer (42). A second (smaller) concentric hemispherical membrane (93) within the first is permanently attached to the layer (42) by heat-sealing to form a hemispherical pouch (95). The pouch (95) communicates with the inlet pipe (46) and is thus effectively an inlet manifold, from which pipes (97) radiate hemispherically and run to the wound bed to end in apertures (98). The pipes (97) deliver the circulating fluid directly to the wound bed via the apertures (98).

(69) The chamber (94) communicates with the outlet pipe (47) and is thus effectively an outlet manifold from which tubules (99) radiate hemispherically and run to the wound bed to end in openings (100). The tubules (99) collect the fluid directly from the wound via the openings (100).

(70) Referring to FIGS. 8a to 8d, one form of the dressing is provided with a square backing layer (42) and first tube (101) extending from the inlet pipe (46), and second tube (102) extending from the outlet pipe (47) at the points at which they pass through the backing layer, to run over the wound bed.

(71) These pipes (101), (102) have a blind bore with orifices (103), (104) along the pipes (101), (102). These pipes (101), (102) respectively form an inlet pipe or outlet pipe manifold that delivers the circulating fluid directly to the wound bed or collects the fluid directly from the wound respectively via the orifices.

(72) In FIGS. 8a and 8d, one layout of each of the pipes (101), (102) as inlet pipe and outlet pipe manifolds is a spiral.

(73) In FIG. 8b, the layout is a variant of that of FIGS. 8a and 8b, with the layout of the inlet manifold (101) being a full or partial torus, and the outlet manifold (102) being a radial pipe.

(74) Referring to FIG. 8c, there is shown another suitable layout in which the inlet manifold (101) and the outlet manifold (102) run alongside each other over the wound bed in a boustrophedic pattern, i.e. in the manner of ploughed furrows.

(75) Referring to FIGS. 9a to 9d, there are shown other suitable layouts for deeper wounds, which are the same as shown in FIGS. 8a to 8d. The square backing layer (42) however has a wound filler (110) under, and may be permanently attached to, the backing layer (42), with an adhesive film (not shown) or by heat-sealing, which is an inverted hemispherical solid integer, here a resilient elastomeric foam, formed of a thermoplastic, preferably a cross-linked plastics foam.

(76) Under the latter is a circular upwardly dished sheet (111) which conforms to, but is a separate structure, permanently unattached to, the solid filler (110). Through the sheet (111) pass the inlet pipe (46) and the outlet pipe (47), to run over the wound bed. These pipes (101), (102) again have a blind bore with orifices (103), (104) along the pipes (101), (102).

(77) Alternatively (as in FIGS. 5a and 5b), where appropriate the dressing may be provided in a form in which the circular upwardly dished sheet (111) functions as the backing layer and the solid filler (110) sits on the sheet (42) as the backing layer, rather than under it. The filler (110) is held in place with an adhesive film or tape, instead of the backing layer (42).

(78) In FIGS. 10a to 10c, inlet and outlet manifolds for the wound dressings for respectively delivering fluid to, and collecting fluid from, the wound, are formed by slots in and apertures through layers permanently attached to each other in a stack.

(79) Thus, in FIG. 10a there is shown an exploded isometric view of an inlet manifold and outlet manifold stack (120) of five square coterminous thermoplastic polymer layers, being first to fifth layers (121) to (125), each attached with an adhesive film (not shown) or by heat-sealing to the adjacent layer in the stack (120).

(80) The topmost (first) layer (121) (which is the most distal in the dressing in use) is a blank square capping layer.

(81) The next (second) layer (122), shown in FIG. 10b out of the manifold stack (120), is a square layer, with an inlet manifold slot (126) through it. The slot (126) runs to one edge (127) of the layer (122) for connection to a mating end of a fluid inlet tube ((not shown), and spreads into four adjacent branches (128) in a parallel array with spaces therebetween.

(82) The next (third) layer (123) is another square layer, with inlet manifold apertures (129) through the layer (123) in an array such that the apertures (129) are in register with the inlet manifold slot (126) through the second layer (122) (shown in FIG. 10b).

(83) The next (fourth) layer (124), shown in FIG. 10c out of the manifold stack (120), is another square layer, with inlet manifold apertures (130) through the layer (124) in an array such that the apertures (130) are in register with the apertures (129) through the third layer (123).

(84) It also has an outlet manifold slot (131) through it.

(85) The slot (131) runs to one edge (132) of the layer (124) on the opposite side of the manifold stack (120) from the edge (127) of the layer (122), for connection to a mating end of a fluid outlet tube (not shown).

(86) It spreads into three adjacent branches (133) in a parallel array in the spaces between the apertures (130) in the layer (124) and in register with the spaces between the apertures (129) in the layer (122).

(87) The final (fifth) layer (125) is another square layer, with inlet manifold apertures (134) through the layer (125) in an array such that the apertures (134) are in register with the inlet manifold apertures (130) through the fourth layer (124) (in turn in register with the apertures (129) through the third layer (123). It also has outlet manifold apertures (135) in the layer (125) in an array such that the apertures (135) are in register with the outlet manifold slot (131) in the fourth layer (124).

(88) It will be seen that, when the layers (121) to (125) are attached together to form the stack (120), the topmost (first) layer (121), the inlet manifold slot (126) through the second layer (122), and the third layer (123) cooperate to form an inlet manifold in the second layer (122), which is in use is connected to a mating end of a fluid inlet tube (not shown).

(89) The inlet manifold slot (126) through the second layer (122), and the inlet manifold apertures (129), (130) and (134) through the layers (123), (124) and (125), all being mutually in register, cooperate to form inlet manifold conduits though the third to fifth layers (123), (124) and (125) between the inlet manifold in the second layer (122) and the proximal face (136) of the stack (120).

(90) The third layer (121), the outlet manifold slot (131) through the fourth layer (124), and the fifth layer (125) cooperate to form an outlet manifold in the fourth layer (124), which is in use is connected to a mating end of a fluid outlet tube (not shown).

(91) The outlet manifold slot (131) through the fourth layer (124), and the outlet manifold apertures (135) through the fifth layer (125), being mutually in register, cooperate to form outlet manifold conduits though the fifth layer (125) between the outlet manifold in the fourth layer (124) and the proximal face (136) of the stack (120).

(92) Referring to FIG. 11, the apparatus (1) for aspirating, irrigating and/or cleansing wounds is a variant of the apparatus (1) of FIG. 1.

(93) It has bypass (711) around the pump (17), as a protection of the pump against any blockage in the system.

(94) It is activated automatically by appropriate means, e.g. it is normally blocked by a bursting disc (not shown), or a pressure-activated motorised valve. An alternative to the by-pass (711) is a pressure sensor in the system that will detect excessive load or pressure, and shut down the pump. Referring to FIG. 12, the apparatus (1) for aspirating, irrigating and/or cleansing wounds is a variant of the apparatus (1) of FIG. 2.

(95) The latter is a two-phase system with a dialysis unit (21), but is one in which dialytic fluid passes only once across the surface of the dialytic membrane (28) in the first chamber (25) from a dialysate reservoir (not shown) to waste via a second bleed T-valve (36) into, e.g. a collection bag (not shown).

(96) This variant has a dialysate recirculation tube (811) running between a first T-valve (816) on the inlet side of the dialysate pump (23) and a second T-valve (817) to permit the pump (23) to recirculate the dialysate once the circuit is primed in multiple passes through the dialysis unit (21).

(97) The operation of the system will be apparent to the skilled person. Referring to FIGS. 13 to 15, these forms of the dressing are provided with a wound filler (348) under a circular backing layer (342).

(98) This comprises respectively a generally downwardly domed or toroidal, or oblately spheroidal conformable hollow body, defined by a membrane (349) which is filled with a fluid, here air or nitrogen, that urges it to the wound shape.

(99) The filler (348) is permanently attached to the backing layer via a boss (351), which is e.g. heat-sealed to the backing layer (342).

(100) An inflation inlet pipe (350), inlet pipe (346) and outlet pipe (347) are mounted centrally in the boss (351) in the backing layer (342) above the hollow body (348). The inflation inlet pipe (350) communicates with the interior of the hollow body (348), to permit inflation of the body (348). The inlet pipe (346) extends in a pipe (352) effectively through the hollow body (348). The outlet pipe (347) extends radially immediately under the backing layer (342).

(101) In FIG. 13a-b, the pipe (352) communicates with an inlet manifold (353), formed by a membrane (361) with apertures (362) that is permanently attached to the filler (348) by heat-sealing. It is filled with foam (363) formed of a suitable material, e.g. a resilient thermoplastic. Preferred materials include reticulated filtration polyurethane foams with small apertures or pores.

(102) In FIG. 14, the outlet pipe (347) communicates with a layer of foam (364) formed of a suitable material, e.g. a resilient thermoplastic. Again, preferred materials include reticulated filtration polyurethane foams with small apertures or pores.

(103) In all of FIGS. 13, 14 and 15, in use, the pipe (346) ends in one or more openings that deliver the irrigant fluid directly from the wound bed over an extended area.

(104) Similarly, the outlet pipe (347) effectively collects the fluid radially from the wound periphery when the dressing is in use.

(105) Referring to FIG. 16a-b, the dressing is also provided with a wound filler (348) under a circular backing layer (342).

(106) This also comprises a generally toroidal conformable hollow body, defined by a membrane (349) which is filled with a fluid, here air or nitrogen, that urges it to the wound shape.

(107) The filler (348) may be permanently attached to the backing layer (342) via a first boss (351) and a layer of foam (364) formed of a suitable material, e.g. a resilient thermoplastic. Again, preferred materials include reticulated filtration polyurethane foams with small apertures or pores.

(108) The first boss (351) and foam layer (364) are respectively heat-sealed to the backing layer (342) and the boss (351).

(109) An inflation inlet pipe (350), inlet pipe (346) and outlet pipe (347) are mounted centrally in the first boss (351) in the backing layer (342) above the toroidal hollow body (348).

(110) The inflation inlet pipe (350), inlet pipe (346) and outlet pipe (347) respectively each extend in a pipe (353), (354) and (355) through a central tunnel (356) in the hollow body (348) to a second boss (357) attached to the toroidal hollow body (348).

(111) The pipe (353) communicates with the interior of the hollow body (348), to permit inflation of the body (348). The pipe (354) extends radially through the second boss (357) to communicate with an inlet manifold (352), formed by a membrane (361) that is permanently attached to the filler (348) by heat-sealing in the form of a reticulated honeycomb with openings (362) that deliver the irrigant fluid directly to the wound bed over an extended area. The pipe (355) collects the fluid flowing radially from the wound centre when the dressing is in use.

(112) This form of the dressing is a more suitable layout for deeper wounds

(113) In FIG. 17, the dressing is similar to that of FIG. 16, except that the toroidal conformable hollow body, defined by a membrane (349), is filled with a fluid, here a solid particulates, such as plastics crumbs or beads, rather than a gas, such as air or an inert gas, such as nitrogen or argon, and the inflation inlet pipe (350) and pipe (353) are omitted from the central tunnel (356).

(114) Examples of contents for the body (348) also include gels, such as silicone gels or preferably cellulosic gels, for example hydrophilic cross-linked cellulosic gels, such as Intrasite™ cross-linked materials. Examples also include aerosol foams, and set aerosol foams, e.g. CaviCarer™ foam.

(115) Referring to FIGS. 18a-b and 19, another form for deeper wounds is shown. This comprises a circular backing layer (342) and a chamber (363) in the form of a deeply indented disc much like a multiple Maltese cross or a stylised rose.

(116) This is defined by an upper impervious membrane (361) and a lower porous film (362) with apertures (364) that deliver the irrigant fluid directly from the wound bed over an extended area. A number of configurations of the chamber (363) are shown, all of which are able to conform well to the wound bed by the arms closing in and possibly overlapping in insertion into the wound.

(117) In a particular design of the chamber (363), shown lowermost, on of the arms extended and provided with an inlet port at the end of the extended arm. This provides the opportunity for coupling and decoupling the irrigant supply remote from the dressing and the wound in use.

(118) An inlet pipe (346) and outlet pipe (347) are mounted centrally in a boss (351) in the backing layer (342) above the chamber (363). The inlet pipe (346) is permanently attached to, and communicate with the interior of, the chamber (363), which thus effectively forms an inlet manifold. The space above the chamber (363) is filled with a loose gauze packing (364).

(119) In FIG. 18, the outlet pipe (347) collects the fluid from the interior of the dressing from just under the wound-facing face (343) of the backing layer (342).

(120) A variant of the dressing of FIG. 18 is shown in FIG. 19. The outlet pipe (347) is mounted to open at the lowest point of the space above the chamber (363) into a piece of foam (374).

(121) In FIG. 20, the dressing is similar to that of FIG. 13, except that the inlet pipe (352) communicates with an inlet manifold (353), formed by a membrane (361) with apertures (362), over the upper surface of the generally downwardly domed wound hollow filler (348), rather than through it.

(122) In FIG. 22, the dressing is similar to that of FIG. 14, with the addition of an inlet manifold (353), formed by a membrane (361) with apertures (362), over the lower surface of the generally downwardly domed annular wound hollow filler.

(123) In FIG. 21, the generally downwardly domed annular wound hollow filler is omitted.

(124) Referring to FIG. 23, another form for deeper wounds is shown. An inlet pipe (346) and outlet pipe (347) are mounted centrally in a boss (351) in the backing layer (342) above a sealed-off foam filler (348). The inlet pipe (346) is permanently attached to and passes through the filler (348) to the wound bed. The outlet pipe (347) is attached to and communicates with the interior of, a chamber (363) defined by a porous foam attached to the upper periphery of the filler (348). The chamber (363) thus effectively forms an outlet manifold.

(125) In FIG. 24, the foam filler (348) is only partially sealed-off. The inlet pipe (346) is permanently attached to and passes through the filler (348) to the wound bed. The outlet pipe (347) is attached to and communicates with the interior of the foam of the filler (348). Fluid passes into an annular gap (349) near the upper periphery of the filler (348) into the foam, which thus effectively forms an outlet manifold.

(126) FIGS. 25 and 26 show dressings in which the inlet pipe (346) and outlet pipe (347) pass through the backing layer (342).

(127) In FIG. 25, they communicates with the interior of a porous bag filler (348) defined by a porous film (369) and filled with elastically resilient plastics bead or crumb.

(128) In FIG. 26, they communicate with the wound space just below a foam filler (348). The foam (348) may CaviCare™ foam, injected and formed in situ around the pipes (346) and (347).

(129) Referring to FIG. 27, the apparatus (1) for aspirating, irrigating and/or cleansing wounds is a major a variant of the apparatus shown in FIG. 1.

(130) The device for moving fluid through the wound and means for fluid cleansing (17) in FIG. 1 is a peristaltic pump (18), e.g. preferably a small portable peristaltic pump, acting on the fluid circulation tube (13) downstream of the dressing (2) to apply a low negative pressure on the wound.

(131) In the apparatus (1) shown in FIG. 27, the peristaltic pump (18) is replaced by: a) a peristaltic pump, acting on the fluid supply tube (7) upstream of the dressing (2), and b) a vacuum pump assembly with pressure regulating means, acting on the fluid circulation tube (13) downstream of the dressing (2),
to apply a low negative pressure on the wound.

(132) The vacuum pump assembly comprises a tank (911) with an inlet tube (912) connecting to the fluid circulation tube (13) and communicating with the upper part of the tank (911), a waste tube (913) connecting to a waste pump (914) with waste bag (915) and communicating with the lower part of the tank (911), a pump tube (916) connecting to a vacuum pump (918) and communicating with the upper part of the tank (911), and an outlet tube (917) connecting to the fluid circulation tube (13) to the means for cleansing (17) and communicating with the lower part of the tank (911).

(133) The vacuum pump (918) is controlled by a pressure feedback regulator (919) through an electrical line (920), the regulator receiving signals from a tank sensor (921) in the upper part of the tank (911), and a dressing sensor (922) in the wound space respectively via lines (923) and (924).

(134) The operation of the apparatus (1) is similar to that of the apparatus in FIG. 1 mutatis mutandis.

(135) The pressure feedback regulator (919) regulates the pressure at the wound and/or the tank (911).

(136) If the amount of fluid in circulation becomes excessive, e.g. because the wound continues to exude heavily, the waste pump (914) may be started to transfer fluid from the lower part of the tank (911) to the waste bag (915).

(137) The use of the apparatus of the present invention will now be described by way of example only in the following Examples:

Example 1—Microfiltration Removal of Bioburden, Including Micro-Organisms from a Single-Phase System

(138) A single phase circuit essentially as in FIG. 1, but with a sample port S1 between the wound dressing and the pump and a sample port S2 downstream of a sterile 0.22.mu.m filter filtration device as the cleansing means was sterilised by γ-irradiation

(139) Prior to inoculation with the test organism (S. aureus NCTC 10788), the wound reservoir was filled with 45 ml sterile MRD (maximum recovery diluent) and then the MRD was inoculated with the test organism to give a final concentration of 10.sup.4 cfu/ml.

(140) The culture was allowed to pre-circulate around the circuit (bypassing the sterile 0.22 μm filter) prior to being circulated through the filtration device. A sample (0.5 ml) of the pre-circulation fluid was taken from port S1 at 30 and 60 minutes. This was serially diluted in MRD to 10.sup.−3 and duplicate 1 ml tryptone soya agar (TSA) plates were repared from each dilution according to a standard validated protocol. Plates were incubated for at least 72 hours at 32° C. prior to counting.

(141) After 1 hour, the fluid was allowed to circulate through the filtration device. 0.5 ml samples of the circulating fluid were taken from ports S1 at T=10, 30, 50 and 70 minutes and S2 at T=0, 20, 40, 60 and 80 minutes. All samples were enumerated as described above.

(142) Results

(143) TABLE-US-00001 TABLE 1 Bacterial counts of pre-circulation fluid taken from the single phase system Sample time (minutes) Mean count (cfu/ml) Log.sub.10 count (cfu/ml) 30 2.31 × 10.sup.4 4.36 60 1.87 × 10.sup.4 4.27

(144) TABLE-US-00002 TABLE 2 Bacterial counts of post-wound reservoir (port S1) fluid taken from the single phase Exudialysis system Sample time (minutes) Mean count (cfu/ml) Log.sub.10 count (cfu/ml) 10 6.30 × 10.sup.3 3.80 30 4.10 × 10.sup.3 3.61 50 1.77 × 10.sup.3 3.25 70 1.23 × 10.sup.3 3.09

(145) TABLE-US-00003 TABLE 3 Bacterial counts of post-filtration (port S2) fluid taken from the single phase Exudialysis system Sample time (minutes) Mean count (cfu/ml) Log.sub.10 count (cfu/ml) 0 <1.0 × 10.sup.1 <1.00 20 <1.0 × 10.sup.1 <1.00 40 <1.0 × 10.sup.1 <1.00 60  1.0 × 10.sup.1 1.00 80 <1.0 × 10.sup.1 <1.00
Conclusions

(146) The single phase system was able to immediately remove bacterial cells from the wound circuit after passing through 0.22.mu.m filter by approximately 3 logs and cause a gradual reduction in the overall numbers of circulating bacteria.

Example 2—Inhibition of Elastase in a Two-Phase System (Static Second Phase)

(147) a) Preparation of an Immobilised Elastase Antagonist—a Conjugate (‘the Inhibitor’) of 4-(2-aminoethyl)-benzenesulfonyl fluoride (AEBSF) with poly(maleic anhydride-alt-methylvinylether), and with 1% 5-(2-aminoethylamino)-1-naphthalenesulfonic acid (EDANS) Fluorescent Tag

(148) To a magnetically stirred solution of MAMVE (1.646 g, 10.5 mmol units) in DMF (100 ml) was added EDANS (30.4 mg, 0.1 mmol) in DMF (2 ml). After 15 minutes, a solution of AEBSF hydrochloride (2.502 g, 10.4 mmol) and triethylamine (1.056 g, 10.4 mmol) in DMF (20 ml) was added dropwise. After 5 h, this solution was precipitated dropwise into 0.5 M HCl (2000 ml), Buchner filtered and washed with 0.5 M HCl. The product was vacuum desiccated to dryness and stored at −4° C. Yield 3.702 g, 98%.

(149) To a magnetically stirred solution of MAMVE (2.000 g, 12.8 mmol units) in DMF (100 ml) was added EDANS (37.0 mg, 0.1 mmol) in DMF (2 ml). After 15 minutes, a solution of phenethylamine (1.537 g, 12.7 mmol) in DMF (10 ml) was added dropwise. After 5 h, this solution was precipitated dropwise into 0.5 M HCl (2000 ml), Buchner filtered and washed with 0.5 M HCl. The product was vacuum desiccated to dryness and stored at room temperature.

(150) Yield 3.426 g, 97%.

(151) b) Elastase Inhibition

(152) A two-phase circuit essentially as in FIG. 1 was used, with a two-phase cleansing means with static second phase, but with a sample port downstream of a cleansing means.

(153) The cleansing means is a MiCroKros Cross Flow Syringe Filter (Spectrum Labs Inc) PS/400K MWCO 8 cm.sup.2, with two separate chambers, any fluid in the outer being held static.

(154) The outer chamber was filled with 2 mg/ml Inhibitor solution (˜1 ml in TRIS) and connected up to the tubing. The inlet and outlet tubing was placed in a TRIS solution and TRIS was flushed through the inner chamber of the MiCoKros syringe and the tubing for 5 mins. The tubing was then emptied. 2 ml of elastase (0.311 mg/ml) was pipetted into the wound circuit.

(155) The tubes were placed in the reservoir and the pump and the timer were started simultaneously.

(156) 10 microliter samples were taken every hour from the wound circuit for six hours and assayed in the following way immediately after sampling. A control of static elastase was assayed at every time point in order to determine the decrease in activity over the 6 hours.

(157) c) Elastase Activity Assay

(158) The elastase substrate N-Succ-(Ala).sub.3-nitronilide was prepared (10 mg/ml in DMSO). 25 microliter of the N-Succ-(Ala).sub.3-nitronilide (10 mg/ml) was added to 2.475 ml of TRIS in a 4.5 ml capacity disposable cuvette. This mixing was completed 10 mins before the elastase solution was due to be added into the cuvettes (in order to ensure the substrate was mixed well). The 10 microliter sample was then added to each cuvette and mixed well. The sample was incubated at room temp for 40 mins and the absorbance at 405 nm recorded.

(159) Results and Conclusions

(160) TABLE-US-00004 TABLE 1 The absorbance detected after 40 mins incubation (405 nm) for elastase + TRIS. The experiment was repeated in triplicate and control of static elastase was recorded every hour. TRIS Elastase Time/h Run 1 Run 2 Run 3 control 0 0.266 0.284 1 0.255 0.258 0.239 0.283 2 0.271 0.242 0.225 0.284 3 0.219 0.218 0.209 0.291 4 0.208 0.203 0.203 0.277 5 0.197 0.17 0.194 0.304 6 0.198 0.161 0.182 0.288 elastase 0.267 0.289 0.281 final

(161) TABLE-US-00005 TABLE 2 The absorbance detected after 40 mins incubation (405 nm) for elastase + MAMVE-AEBSF. The experiment was repeated in triplicate and control of static elastase was recorded every hour. The average of all the elastase control experiments was used to calculate the 100% activity for 0 h. MAMVE-AEBSF Elastase Time/h Run 1 Run 2 Run 3 control 0 0.362 0.39 0.371 1 0.234 0.308 0.267 0.4 2 0.158 0.215 0.193 0.374 3 0.081 0.161 0.128 0.363 4 0.064 0.12 0.083 0.366 5 0.046 0.073 0.048 0.375 6 0.025 0.061 0.034 0.348

(162) The average of all the elastase control experiments was used to calculate the 100% activity for 0 h.

(163) TABLE-US-00006 TABLE 3 The average % elastase activity for 3 variables, with the SD % Average SD Time/h TRIS AEBSF Time/h TRIS AEBSF 0 100.00 100.00 0 1 88.55 72.47 1 3.61 9.96 2 86.90 50.70 2 8.22 7.73 3 76.07 33.14 3 1.95 10.80 4 72.30 23.92 4 1.02 7.65 5 66.06 14.96 5 5.23 4.04 6 63.70 10.75 6 6.55 5.03

(164) The results indicate that for the elastase+Tris solution there is a 60-70% drop in activity. This can be explained as a dilution effect as the 2 ml of elastase mix with the 1 ml TRIS in the outer chamber (⅔). This indicates that the system is inert to elastase and the complete mixing/diffusion across the membrane occurs within 3 h.

(165) The elastase+MAMVE-AEBSF within the 6 h shows a 90% drop in elastase activity.

Example 3—Sequestration of Iron Ions from a Two-Phase System (Static Second Phase)

(166) A two-phase circuit essentially as in FIG. 1 was used, with a two-phase cleansing means with static second phase, but with a sample port downstream of a cleansing means, the latter being a Slide-A-Lyzer dialysis cassette (Pierce, 10,000 MWCO, 3-15 ml capacity, Product #66410) in a chamber of a Slide-A-Lyzer.

(167) The cassette was loaded with one of the following: a) 5 ml of phosphate buffer saline (PBS), b) starch control (40, 120 and 200 mg/ml) or c) starch-desferrioxamine (DFO) conjugate (supplied by Biomedical Frontiers Inc.) in solution (40, 120 and 200 mg/ml).

(168) Each dialysis cassette was placed in a Slide-A-Lyzer chamber. In this arrangement, the cassette load is separated from the recirculating first fluid by the 10,000 MWCO membrane referred to above.

(169) Transferrin (10 mg/ml, 35 ml volume) was injected into the sample port and circulated around the flow system by a Masterflex pump (Model No. 7523-37) at different flow rates (0.54, 0.82, 1.08 and 1.35 ml/min) for 8 hours.

(170) Samples were collected at 0, 2, 4, 6 and 8 hours.

(171) The iron content of the samples was measured using a ferrozine assay as follows: The sample was mixed with 50 mM acetate buffer, pH 4.8 to liberate iron from transferrin. Ascorbate (30 mM) was added to the sample to reduce released Fe (III) ions to Fe (II) ions. Ferrozine (5 mM) was mixed with the sample forming a coloured complex with Fe (II) ion. The absorbance was measured using UNICAM UV4-100 UV-Vis spectrophotometer V 3.32 (serial no. 022405).

(172) Results and Conclusions

(173) Starch-DFO picked up iron from transferrin in a dose dependent manner over 8 hours. Approximately 20-25% iron removal occurred in the presence of 200 mg/ml of starch-DFO after 8 hours recirculation.

(174) In the presence of different concentrations of starch control or PBS the iron content of transferrin dropped slightly due to a dilution effect but then slowly returned to normal, suggesting that iron pick-up by starch-DFO was mediated by DFO alone.

(175) The iron pick-up profile for transferrin was similar at different flow rates suggesting that flow had no effect on iron transfer across the dialysis membrane.

Example 4—Infusion of Antibiotic from the Second Phase of a Two-Phase System (Moving Second Phase)

(176) A two-phase circulation system essentially as in FIG. 1 with the second (dialysate) circuit essentially as in FIG. 2 was used. The pumps were peristaltic acting on silicone tubing. The second circuit was provided with a reservoir of dialysate with which to modify the wound fluid (50 ml Falcon centrifuge tube). The wound circuit was connected into the ends of a luer-fitting hollow fibre tangential membrane dialysis unit (Spectrum® MicroKros® X14S-100-04N, 8 cm2 surface area, 400 KD Mol. Wt. cut off). The dialysate circuit was connected to the side ports of the same dialysis unit so that flow between the wound circuit and the dialysate circuit were in a counter current direction.

(177) The wound circuit was flushed first with ethanol and then with sterile water as per the manufacturers' instruction. The wound reservoir was filled with 20 ml of sterile water. The wound pump was run at a speed setting of 100, which generated a measured flow rate of 2.09 ml.sup.−1 in the wound circuit. The dialysate circuit was flushed first with ethanol and then with sterile water as per the manufacturers instruction. The dialysate reservoir was filled with 20 ml of sterile water. The dialysate pump was run at a speed setting of 100, which generated a measured flow rate of 1.93 ml min.sup.−1 in the dialysate circuit. Samples (1 ml) were removed from the wound and the dialysate reservoirs by means of a length of silicone tube with a luer fitting attached to a 2 ml syringe

(178) At the start of the experiment, 5 ml of sterile water was removed from the dialysate reservoir and 5 ml of a 5 mg ml.sup.−1 solution of gentamycin sulphate was added (EP standard gentamycin sulphate, CRS; (activity 616 IU mg.sup.−1)). Both the wound and the dialysate pumps were started at the same time. Samples were removed from the dialysate circuit and the wound circuit at intervals over 230 minutes. No volumes were replaced during the experiment.

(179) Samples (1 ml) were diluted with 2 ml of sterile water and the UV absorbance at 190 nm was checked to get an approximate measure of the movement of gentamycin from the dialysate circuit to the wound circuit using a previously generated standard curve.

(180) Samples were subsequently analysed with a quantitative zone of inhibition assay for gentamycin activity according to an assay that uses Staphylococcus epidermidis as the indicator bacteria.

(181) Results and Conclusions

(182) The results of the antimicrobial activity-zone of inhibition assays of the fluid show that the level of gentamycin in the wound circuit increases steadily over 230 min with the rate of increase slowing as the levels of drug in the two circuits approach each other. The gentamycin levels in the dialysate circuit show a steady decrease as expected if drug is moving from the dialysate circuit to the wound circuit. At the pressure and flow rates useful in clinical practice, drugs for wound healing can be delivered in acceptable quantities and on an acceptable timescale.

Example 5—Regeneration of Glutathione (Reduction of Oxidised Glutathione (GSSG) to Glutathione (GSH) by Localised Glutathione Reductase (GR) and Cofactor NADP (Reduced Form) in a Two-Phase System (Static Second Phase)

(183) A two-phase circuit essentially as in FIG. 1 was used, with a two-phase cleansing means with static second phase, but with a sample port downstream of a cleansing means, the latter being a Slide-A-Lyzer dialysis cassette (Pierce, 10,000 MWCO, 3-15 ml capacity, Product #66410) in a chamber of a Slide-A-Lyzer.

(184) Into the internal cavity of separate 15 ml capacity Slide-A-Lyzer cassettes was injected 5 ml of each stock solution: a) 2 mg/ml NADP prepared in distilled water (NADP) b) 2 mg/ml Glutathione reductase prepared in NADP stock solution (GR+NADP) c) 2 mg/ml Glutathione reductase prepared in distilled water (GR) in triplicate.

(185) The cassettes were laid flat and into the upper, outer cavity was aliquoted 15 ml of GSSG stock solution (50 microM GSSG prepared in distilled water (30.6 mg/l). This was circulated around the first phase circuit. The latter was sampled (1 ml) every hour for 6 h in total into 1.5 ml capacity disposable UV cuvettes. At the end of this period, each aliquot was assayed using a Glutathione Assay Kit (from Calbiochem). Triplicates were averaged and SD determined for each data point. These data were plotted as GSSG concentration versus time for each of the three control systems.

(186) Results & Conclusions

(187) GSSG was depleted by the combination of GR and its cofactor NADP to a significantly greater extent than by GR or NADP alone. Thus depletion is not attributable to non-specific binding. Approximately 40% of GSSG was depleted in 6 h at the stated enzyme and cofactor concentrations.

Example 6—Degradative Removal of Bacterial Autoinducers from a Single-Phase System

(188) The exchange of extra cellular signalling molecules called auto-inducers is used by bacteria and is essential to the co-ordinatation of the expression of key bacterial virulence genes activated at a critical bacterial cell density, and thus to achieving successful bacterial colonization and invasion of tissue. The system is called Quorum Sensing. Conversely, (usually enzymic) degradation or sequestration of the autoinducer species is one way to disrupt the essential communication and aid the prevention of infection in wounds.

(189) The AiiA enzyme is a degrader of the 3-oxododecylhomoserine lactone signal molecule which is used by S. aureus as an autoinducer.

(190) The AiiA enzyme used is one produced at the University of Nottingham and is bound to a maltose binding protein.

(191) a) Preparation of AiiA Enzyme Bound to a Polymer Support

(192) Cyanogen bromide activated Sepharose 6 MB (from Sigma) (200-300 μm diameter for a higher through-flow rate) were washed in 1 mM hydrochloric acid and allowed to soak and swell for a period of 30 minutes. The gel was washed with multiple volumes of distilled water and then with NaHCO.sub.3/NaCl pH 8.5 and used immediately.

(193) The AiiA enzyme solution (approx. 1 mg/ml) was added to the polymer support beads and allowed to stand at 4° C. overnight. The coupled beads were washed with pH 8.5 NaHCO.sub.3/NaCl and stored as a slurry. The washings from the beads were also collected in order to determine the amount of uncoupled enzyme and hence the coupling efficiency.

(194) Blank, uncoupled beads were used as a control.

(195) Different amounts of the enzyme coupled beads, 1 mg, 10 mg and 100 mg, are trapped in a chamber defined by two glass frits across a cylindrical glass cylinder with axial inlet and outlet ports for throughflow, which formed the cleansing means in a single phase system, which also has a sample port downstream of a cleansing means. A 10 microM stock of 3-oxododecylhomoserine lactone (ODHSL) is pumped through the chamber at 1.93 ml min.sup.−1 and 37° C. for 6 hr.

(196) The circulating fluid is sampled (1 ml) every hour for 6 h in total into 1.5 ml capacity disposable UV cuvettes.

(197) At the end of this period, each aliquot was assayed using the assay of Swift et al. 1997, J. Bacteriol. 179: 5271-5281, which uses bioluminescence-based plasmid reporter systems in E. coli. The 100 mg sample shows an 86% reduction in ODHSL concentration in 6 hours.