Apparatus and Method for Cardiac Tissue Modulation by Topical Application of Vacuum to Minimize Cell Death and Damage

Abstract

A method and apparatus are provided for treating cardiac tissue to modulate ischemic heart tissue with topical sub-atmospheric pressure to minimize cell death and damage.

Claims

1. An apparatus for treating damaged cardiac tissue, comprising: a porous bio-incorporable material for treating damaged cardiac tissue having a pore structure configured to permit gaseous communication between one or more pores of the porous material and the cardiac tissue to be treated, the porous material comprising pores sufficiently small at a surface of the porous material for placement proximate the damaged cardiac tissue to prevent the ingrowth of tissue therein and having a selected surface disposed away from the cardiac tissue to be treated having a pore size sufficiently large to promote the formation of granulation tissue thereat; a bio-incorporable cover for placement over the damaged cardiac tissue for sealing engagement with cardiac tissue proximate the damaged cardiac tissue for maintaining sub-atmospheric pressure at the damaged cardiac tissue; and a vacuum source for producing subatmospheric pressure disposed in gaseous communication with the porous material for distributing the sub-atmospheric pressure to the cardiac tissue to be treated.

2. The apparatus according to claim 1, wherein the porous material comprises myocardial cells.

3. The apparatus according to claim 1, wherein the cover comprises myocardial cells.

4. The apparatus according to claim 1, wherein the porous material comprises peripheral muscle cells.

5. The apparatus according to claim 1, further comprising a porous intermediate material for contacting the damaged heart tissue, the porous intermediate material disposed below and in contact with the porous material.

6. The apparatus according to claim 1, wherein the cover comprises a vacuum port disposed in gaseous communication with the vacuum source for receiving sub-atmospheric pressure from the vacuum source.

7. The apparatus according to claim 1, wherein the cover comprises an adhesive seal for adhering and sealing the cover to cardiac tissue surrounding the damaged cardiac tissue.

8. The apparatus according to claim 1, wherein the cover comprises a self-adhesive sheet.

9. The apparatus according to any one of claims 1-4, wherein the cover comprises an electrospun material.

10. The apparatus according to any one of claims 1-4, wherein the cover comprises poly 1,8-octanediol citrate.

11. The apparatus according to any one of claims 1-4, wherein the cover comprises collagen.

12. The apparatus according to any one of claims 1-4, wherein the cover comprises a diol citrate.

13. The apparatus according to any one of claims 1-4, wherein the cover comprises a cast material.

14. The apparatus according to any one of claims 1-4, wherein the cover comprises chitosan.

15. The apparatus according to any one of claims 1-4, wherein the cover comprises polylactic acid.

16. The apparatus according to any one of claims 1-4, wherein the cover comprises a plurality of printed layers.

17. The apparatus according to any one of claims 1-4, wherein the porous material comprises a plurality of printed layers.

18. The apparatus according to claim 1, wherein the vacuum source is configured to maintain a sub-atmospheric pressure of about 50 mm Hg below atmospheric pressure at the damaged cardiac tissue.

19. The apparatus according to claim 1, wherein the vacuum source is configured to maintain sub-atmospheric pressure of between about 50 and 125 mm Hg below atmospheric pressure at the damaged cardiac tissue.

20. The apparatus according to claim 1, wherein the porous material comprises a polyethylene, polyurethane, and/or polyester material.

21. The apparatus according to claim 1, wherein the porous material comprises a pore size smaller than the size of fibroblasts.

22. The apparatus according to claim 1, wherein the porous material comprises collagen.

23. The apparatus according to claim 1, wherein the porous material comprises chitosan.

24. The apparatus according to claim 1, wherein the porous material comprises polycaprolactone.

25. The apparatus according to claim 1, wherein the porous material comprises a polyglycolic and/or polylactic acid.

26. The apparatus according to claim 1, wherein the porous material comprises a porous, open-cell collagen material.

27. The apparatus according to claim 1, wherein the porous material comprises a porous synthetic polymer material.

28. The apparatus according to claim 1, wherein the porous material comprises at least one of a porous sheet and a flexible, sheet-like mesh.

29. The apparatus according to claim 1, wherein the porous material comprises two or more layers, with the layer closest to the damaged cardiac tissue containing pores sufficiently small at the interface between the porous material and the damaged cardiac tissue to prevent the growth of tissue therein.

30. The apparatus according to claim 1, wherein the porous material comprises a pore size large enough to allow movement of proteins the size of albumin therethrough to permit undesirable compounds to be removed.

31. The apparatus according to claim 1, wherein the vacuum source comprises a vacuum pump.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

[0020] The foregoing summary and the following detailed description of the preferred embodiments of the present invention will be best understood when read in conjunction with the appended drawings, in which:

[0021] FIG. 1 schematically illustrates a partial cross-sectional view of an exemplary configuration of an apparatus of the present invention in situ prior to the application of sub-atmospheric pressure;

[0022] FIG. 2 schematically illustrates the partial cross-sectional view of FIG. 1 as a sub-atmospheric pressure is being applied;

[0023] FIG. 3 schematically illustrates the partial cross-sectional view of FIG. 1 after sub-atmospheric pressure has been applied;

[0024] FIG. 4 schematically represents a cross-sectional view of an exemplary configuration of the present invention in situ in which the tissues overlying the heart have been closed around the tube to create a space capable of maintaining a vacuum so no overlay cover is required;

[0025] FIG. 5 schematically represents a partial cross-sectional view of the apparatus of the present invention in situ in which the porous material is layered with a smaller pore layer adjacent to the damaged tissue and a layer with larger pores above the smaller pore layer;

[0026] FIG. 6 schematically represents a view of an exemplary configuration of a porous material of the present invention in which only one side of the porous material is open and not sealed;

[0027] FIG. 7 schematically represents a cross-sectional view of an exemplary configuration of the present invention in which an overlay cover has been placed over the porous material and potential leaks sealed with fibrin glue;

[0028] FIG. 8 schematically represents a partial cross-sectional view of an exemplary configuration of the present invention in which the edges of the overlay cover have been turned under;

[0029] FIG. 9 schematically represents a cross-sectional view of an exemplary configuration of the present invention in which the overlay cover is self adhesive;

[0030] FIG. 10 schematically represents an exemplary configuration of the cover of the present invention in which the tube passes through the overlay cover;

[0031] FIG. 11 schematically represents a partial cross-sectional view of the vacuum tube attaching to the overlay cover;

[0032] FIG. 12 schematically represents a kidney, with artery and vein;

[0033] FIG. 13 schematically represents an open clamshell or bi-valve chamber for application of sub-atmospheric pressure; and

[0034] FIG. 14 schematically represents a kidney disposed within the chamber of FIG. 13.

DETAILED DESCRIPTION OF THE INVENTION

[0035] Referring now to the figures, wherein like elements are numbered alike throughout, the present invention relates to devices and methods that use sub-atmospheric (or negative) pressure for treating damaged cardiac tissue, where damaged tissue is defined to include tissue that is injured, compromised, or in any other way impaired, such as damage due to trauma, disease, infection, surgical complication, or other pathologic process, for example. More specifically, the devices and methods of the present invention can effect treatment of myocardial infarction.

[0036] An exemplary configuration of a sub-atmospheric cardiac treatment device 100 of the present invention may include a vacuum source 30 for supplying sub-atmospheric pressure via a tube 20 to a porous material 10, such as a bio-incorporable porous material, disposed in direct or indirect contact with the damaged cardiac tissue 7, FIGS. 1-4. As used here, indirect contact is defined to mean placement of an intermediate material for transmitting sub-atmospheric pressure in contact with both the damaged cardiac tissue 7 and the porous material 10. In this regard, the porous material 10 may be structured to deliver and distribute sub-atmospheric pressure to the damaged cardiac tissue 7. Alternatively, the porous material 10 may be comprised of a material that needs to be removed after sub-atmospheric therapy is given, which could require a second surgery. The cardiac treatment device 100 may be applied to a patient by locating a porous material 10 in contact with the damaged cardiac tissue 7 to provide gaseous communication between one or more pores of the porous material 10 and the damaged cardiac tissue 7. A tube 20 may be connected to the porous material 10 at a distal end 22 of the tube 20, and the porous material 10 may be sealed in situ by sutures 8 in the skin 1 and subcutaneous tissues 2 to provide a region about the damaged cardiac tissue 7 for maintaining sub-atmospheric pressure, FIG. 4. The proximal end 24 of the tube 20 may be attached to a vacuum source 30 to operably connect the porous material 10 to the vacuum source 30 for producing sub-atmospheric pressure at the damaged cardiac tissue 7 upon activation of the vacuum source 30. Optionally, an overlay cover 40, such as a bio-incorporable overlay cover 40, may be located over the damaged cardiac tissue 7 and sealed proximate the damaged cardiac tissue 7 to maintain sub-atmospheric pressure at the damaged cardiac tissue 7.

[0037] Turning to FIGS. 1-4 in greater detail, an exemplary configuration of a sub-atmospheric pressure cardiac treatment device 100 of the present invention is illustrated in partial cross-section with the porous material 10 in contact with the damaged cardiac tissue 7. An overlay cover 40 covers the porous material 10 and may extend onto healthy cardiac tissue 6 creating an enclosed space 48. An adhesive 41, such as fibrin glue or other material, may be placed between the overlay cover 10 and the healthy cardiac tissue 6. The adhesive 41 may also or alternatively be placed around the periphery of the overlay cover 10 to prevent leaks, and may also be placed around a passthrough 52 where the tube exits from the overlay cover 10 to prevent leaks. FIG. 1 depicts the device 100 prior to application of sub-atmospheric pressure. FIG. 2 depicts the device 100 as sub-atmospheric pressure is being applied, and the enclosed space 48 decreases in volume as fluid and gas are evacuated from the enclosed space 48 and the overlay cover 40 conforms to the porous material 10. FIG. 3 depicts the device 100 after sub-atmospheric pressure has been applied, with the overlay cover 40 conforming to the shape of the porous material 10.

[0038] Turning to FIG. 4 specifically, an exemplary configuration of a sub-atmospheric cardiac treatment device 100 of the present invention is illustrated in situ in a patient with surrounding tissues shown in partial cross-section. The tissues illustrated include the skin 1 and subcutaneous tissue 2, muscle 3, bone 4, pericardium 5, healthy non-damaged cardiac tissue 6, the damaged cardiac tissue 7, and the pleural tissues 12. To provide access to the damaged cardiac tissue 7, a portion of the pericardium 5 may be missing due to surgical dissection or injury. A porous material 10, such as an open-cell collagen material, may be placed in the subcutaneous space in contact (direct or indirect) with the cardiac tissue 7 to be treated with sub-atmospheric pressure to decrease edema and interstitial pressure, oxygen radicals, inflammatory mediators, and other molecules which may adversely affect cellular resuscitation or viability within the damaged cardiac tissues to improve physiologic function, for example. The distal end 22 of the tube 20 may connect to the porous material 10 and the tube 20 may exit the body through an incision. The tube 20 may have one or more fenestrations 23 in that portion of the tube 20 in contact with the porous material 10, FIG. 6. The tissues between the cardiac tissue 7 up to and including the skin 1 are closed with, for example sutures 8, to create an airtight seal capable of maintaining a vacuum. When sub-atmospheric pressure is applied, the edges of the incised tissues 1-5 are drawn together and the pleural tissues 12 are drawn toward the porous material to help maintain the vacuum. The proximal end of the tube 24 may be connected to a vacuum source 30 and the level of sub-atmospheric pressure controlled by a controller 32. The vacuum source 30 may include a canister to collect any fluid removed.

[0039] The cover 40 may serve to further confine the region about the damaged cardiac tissue 7 at which sub-atmospheric pressure is maintained. That is, as illustrated in FIGS. 1-3, 7-9, the cover 40, 50 provides an enclosed space/region 48, 58 about the damaged cardiac tissue 7 under the cover 40, 50, which can serve to isolate the tissues exterior to the cover 40, 50 from exposure to the sub-atmospheric pressure applied to the damaged cardiac tissue 7. In contrast, as illustrated in FIG. 4, in the absence of an overlay cover, sub-atmospheric pressure delivered to the porous material 10 and damaged cardiac tissue 7 may draw the surrounding tissues, such as the pericardium 5 and pleural tissues 12, inward towards the tube 20 and porous material 10 along the directions of the arrows shown in FIG. 4. In this regard the stretched and/or moved tissues, such as pericardium 5 and pleural tissues 12 can help to confine the applied sub-atmospheric pressure to a region between the pericardium 5 and the damaged cardiac tissue 7. In addition the covers 40, 50 may further protect the damaged cardiac tissue 7 from exogenous infection and contamination beyond the protection already afforded by the porous material 10 and sutured skin 1 and subcutaneous tissue 2. Likewise, the covers 40, 50 may further protect the damaged cardiac tissue 7 from the spread of infections from the surrounding tissues (such as cardiac abscesses and mediastinitis).

[0040] To assist in maintaining the sub-atmospheric pressure at the damaged cardiac tissue 7, a flexible overlay cover 40 (FIG. 7), or a self adhesive flexible overlay cover 50 (FIG. 9) may be provided over the damaged cardiac tissue 7 to provide a region 48, 58 about the damaged cardiac tissue 7 where sub-atmospheric pressure may be maintained, FIGS. 7, 8. Specifically, with reference to FIGS. 7, 8, and 9, an overlay cover 40, 50 may be provided over the damaged cardiac tissue 7 and porous material 10 by adhering the cover 40, 50 to cardiac tissues proximate the damaged cardiac tissue 7 to define an enclosed region 48, 58 about the damaged cardiac tissue 7 and porous material 10. For instance, the cover 40 may be glued to cardiac tissue using an adhesive 41, such as a fibrin glue. The adhesive 41 may comprise an auto-polymerizing glue and/or may desirably include a filler to provide the adhesive 41 with sufficient bulk to permit the adhesive 41 to conform to the shapes of the potentially irregular surfaces which the adhesive 41 contacts. The adhesive 41 may be provided as a separate component or as a portion of the cover 40. For the flexible overlay cover 40, an outside edge or border of the flexible overlay cover 40 may either be rolled away from (or laid flat on) the non-damaged cardiac tissue 6 or rolled under (or toward) the damaged cardiac tissue 7, FIGS. 7, 8. The adhesive 41 may be placed between the edge of the overlay cover 40 and the healthy cardiac tissue 6 to promote an airtight seal. The adhesive 41 may also be placed around the tube 20 where it exits through the overlay cover 40. Alternatively, a self-adhesive flexible overlay cover 50 may be curled out away from the damaged cardiac tissue 7 so that the underside of the cover 50 (that side facing the porous material 10) may then contact with the surrounding non-damaged cardiac tissue 6, FIG. 9.

[0041] In addition to an open-cell collagen material, the porous material 10 may also include a polyglycolic and/or polylactic acid material, a synthetic polymer, a flexible sheet-like mesh, an open-cell polymer foam, a foam section, a porous sheet, a polyvinyl alcohol foam, a polyethylene and/or polyester material, or other suitable materials which may be fabricated by electrospinning, casting, or printing, for example. Such materials include a solution of chitosan (1.33% weight/volume in 2% acetic acid, 20 ml total volume) which may be poured into an appropriately sized mold. The solution is then frozen for 2 hours at 70 C., and then transferred to the lyophylizer and vacuum applied for 24 hours. The dressing may be cross-linked by 2.5%-5% glutaraldehyde vapor for 12-24 hours to provide a cast porous material.

[0042] Additionally, the porous material 10 may be made by casting polycaprolactone (PCL). Polycaprolactone may be mixed with sodium chloride (1 part caprolactone to 10 parts sodium chloride) and placed in a sufficient volume of chloroform to dissolve the components. A desired amount, e.g., 8 ml, of the solution may be poured into an appropriately sized and shaped container and allowed to dry for twelve hours. The sodium chloride may then be leached out in water for 24 hours.

[0043] The overlay cover 40 may also be bio-incorporable and may consist of an electrospun mixture of Type I collagen and poly 1,8-octanediol citrate (POC) (80%:20% weight/weight). The solution concentration may be 15% dissolved in hexafluoro-2 proponal (HFP) with a total volume of 9.5 ml. The solution may then be ejected from a syringe through an 18 gauge needle at a flow rate of 1-3 ml/hour. The voltage may be 25 KV with a working distance of 20-25 cm. The film may then be heat polymerized at 80 C. for 48 hours (of 90 C. for 96 hours) and cross-linked in 2.5%-10% glutaraldehyde vapor for 24 hours.

[0044] It is also possible to use electrospun materials for the porous material 10 and cast materials for the overlay cover 40. One example of a formulation and method for making an electrospun porous material 10 is a combination of collagen Type I:chondroitin-6-sulfate (CS):poly 1,8-octanediol citrate (POC) in a ratio of 76%:4%:20%:by weight. Two solvents were utilized for the collagen/CS/POC. The CS was dissolved in water and the collagen and POC were dissolved in 2,2,2-trifluoroethanol (TFE). A 20% water/80% TFE solution (volume/volume) solution was then used. For electrospinning, the solution containing the collagen:CS:POC mixture was placed in a 3 ml syringe fitted to an 18 Ga needle. A syringe pump (New Era Pump Systems, Wantaugh, N.Y.) was used to feed the solution into the needle tip at a rate of 2.0 ml/hr. A voltage of 10-20 kV was provided by a high voltage power supply (HV Power Supply, Gamma High Voltage Research, Ormond Beach. Fla.) and was applied between the needle (anode) and the grounded collector (cathode) with a distance of 15-25 cm. The dressings were then cross-linked with glutaraldehyde (Grade II, 25% solution) and heat polymerized (80 C.) for 48 hours. It is also possible to electrospin collagen Type I dressings starting with an initial concentration of 80 mg/ml of collagen in 1,1,1,3,3,3-hexafluoro-2-propanol (HFP), then use the same electrospinning conditions as the collagen:CS:POC combination.

[0045] Examples of cast overlay cover formulas include the use of 1,8 poly (octanediol) citrate (POC) or other combinations of diol citrates, which could be 1,6 hexanediol or 1,10 decanediol, for example. To make the cast overlay cover 40, equimolar amounts of anhydrous citric acid and the diol of choice may be combined in a round bottom flask. (As an example: 38.4 g citric acid and 29.2 g octanediol). The solution may be heated in an oil bath for 10 min at 165 C. until melted, then continued to be heated at 140 C. for 45 min. The polymer may be used in this form although unreacted monomers are also present. To remove the unreacted monomer, equivolume amounts of polymer and 100% acetone may be added to a flask and shaken until the polymer is completely dissolved, then poured into an appropriately shaped mold. The acetone may be evaporated overnight in a chemical hood at room temperature. The films may be polymerized at 80 C. for 36 hr and then 18 hr at 110 C.

[0046] Alternatively, to cast overlay covers 40 of chitosan, a solution of 2% acetic acid in water may be added to 1% chitosan weight/volume. (For example 400 l acetic acid may be added to 20 ml water, then 200 mg chitosan added.) Films may be prepared by pouring the mixture directly into the mold and allowing the solution to dry overnight. Cast overlay covers 40 of poly L (lactic acid) or poly D,L (co-glycolic lactic acid) dissolved in chloroform can also be made by pouring the solution into molds and evaporating the solvent (chloroform) off.

[0047] An additional method for creating porous materials 10 and overlay covers 40 is to use thermal inkjet printing technologies. Bio-incorporable materials such as collagen, elastin, hyaluronic acid, alginates, and polylactic/polyglycolic acid co-polymers may be printed. As examples, Type I collagen (Elastin Products Co., Owensville, Mo.) dissolved in 0.05% acetic acid, then diluted to 1 mg/ml in water can be printed, as can sodium alginate (Dharma Trading Co., San Raphael, Calif.) 1 mg/ml in water. A mixture of Type I collagen (2.86 mg/ml in 0.05% acetic acid) and polylactic/polyglycolic acid (PURAC America, Blair, Nebr.) (14.29 mg/ml in tetraglycol (Sigma Aldrich, St. Louis Mo.)) can also be printed. Hardware from a Hewlett Packard 660c printer can be attached to a platform for which the height can be adjusted for printing in layers. With minimal changes to the hardware, no software changes need to be made.

[0048] Turning to FIG. 5, the porous material 10 may comprise layers, with the layer 112 closest to the damaged cardiac tissue containing pores sufficiently small at the interface between the porous material 110 and the damaged cardiac tissue 7 to prevent the growth of tissue therein, e.g., a pore size smaller than the size of fibroblasts and cardiac cells. Otherwise the porous material 110 may stick to the damaged cardiac tissue 7 and cause bleeding or trauma, and potentially even disruption of the ventricular wall when the porous material 110 is removed. Additionally, growth of tissues into the porous material 110 may result in eventual erosion through the ventricular wall or pleural tissues with continual movement and rubbing of the porous material 110 against these tissues if the porous material 110 is left in the patient. Further, growth of tissues into the porous material 110 may result in non-contractible scar formation within the porous material or potential calcification of tissues within the porous material 110 if the porous material 110 is left within the patient. In addition, the pore size at the interface between the porous material 10, 110 and the damaged cardiac tissue 7 may be sufficiently small so as to avoid the excessive production of granulation or scar tissue at the damaged cardiac tissue 7 which may interfere with the physiologic function of the heart. At the same time, the pore size of the porous material 10, 110 may be large enough to allow movement of proteins the size of albumin therethrough to permit undesirable compounds to be removed, such as mediators, degradation products, and toxins.

[0049] The porous material 10, 110 may, however, have a larger pore size (e.g., larger than that of fibroblasts and cardiac cells) interior to the porous material 10, 110 or at any other location of the porous material 10 that is not in contact with cardiac tissue 7. For example, the porous material 110 may comprise a multi-layer structure with a non-ingrowth layer 112 having a sufficiently small pore size to prevent the growth of tissue therein for placement at the cardiac tissue 7, and may have an additional layer 114 of a different material that has a relatively larger pore size in contact with the non-ingrowth layer 112.

[0050] Alternatively, as depicted in FIG. 6, the porous material 210 may be homogeneous in composition and/or morphology. At a location away from the interface with the damaged cardiac tissue, the porous material 210 may have a pore size sufficiently large to promote the formation of granulation tissue at other tissues in the spaces surrounding the damaged cardiac tissue, such as promotion of granulation tissue in areas where cardiac disruption has occurred. In addition, the porous material 210 may have a configuration in which one or more sides or surfaces 212 of the porous material 210 are sealed to prevent the transmission of sub-atmospheric pressure through such a sealed surface 212, while at the same time having at least one surface 214 through which sub-atmospheric pressure may be transmitted. Such a configuration of the porous material 210 can present preferential treatment of tissue on one side of the porous material 210 while not treating tissue on the other side. For instance, the damaged cardiac tissue could be treated with the non-sealed interface on one side 214 of the porous material 210.

[0051] In addition, the porous material 10 may comprise a non-metallic material so that an MRI can be performed while the porous material 10 is in situ. The porous material 10 may also comprise a material that is sufficiently compliant so that it does not interfere with cardiac function. At the same time, the porous material 10 may comprise a material that is sufficiently firm so that the porous material 10 does not collapse so much as to create a pull on, or distortion of, the cardiac tissue 6, 7 that might interfere with cardiac function.

[0052] Turning to FIG. 7, to deliver sub-atmospheric pressure to the porous material 10 for distribution to the damaged cardiac tissue 7, a tube 20 may be connected directly or indirectly in gaseous communication with the porous material 10 at the distal end 22 of the tube 20. For example, the distal end 22 of the tube 20 may be embedded in the porous material 10 or may be placed over the porous material 10. The distal end 22 of the tube 20 may also include one or more fenestrations 23 to assist in delivering the sub-atmospheric pressure to the porous material 10 and the damaged cardiac tissue 7. The tube 20 may extend through an opening in the skin 1 and subcutaneous tissue 2 which may be secured about the tube 20 with a suture 8 to assist in providing a seal about the tube 20. The proximal end 24 of the tube 20 may be operably connected to a vacuum source 30 (e.g., The V.A.C., Model 30015B, Kinetic Concepts, Inc., San Antonio, Tex.) to provide sub-atmospheric pressure that is transmitted via the tube 20 to the porous material 10 and the damaged cardiac tissue 7.

[0053] The vacuum source 30 may include a controller 32 to regulate the production of sub-atmospheric pressure. For instance, the vacuum source 30 may be configured to produce sub-atmospheric pressure continuously or intermittently; e.g., the vacuum source 30 may cycle on and off to provide alternating periods of production and non-production of sub-atmospheric pressure. The duty cycle between production and non-production may be between 1 to 10 (on/off) and 10 to 1 (on/off). In addition, intermittent sub-atmospheric pressure may be applied by a periodic or cyclical waveform, such as a sine wave, or may be cycled after initial treatment to mimic a more physiologic state, such as the heart rate. The sub-atmospheric pressure may also be cycled on-off as-needed as determined by monitoring of the pressure in the damaged cardiac tissue 7. In general, the vacuum source 30 may be configured to deliver sub-atmospheric pressure between atmospheric pressure and 200 mm Hg below atmospheric pressure to minimize the chance that the sub-atmospheric pressure may result in reduction in localized blood flow due to either constriction of capillaries and small vessels or due to congestion (hyperemia) within the damaged cardiac tissue 7 or otherwise be deleterious to the damaged cardiac tissue 7. The application of such a sub-atmospheric pressure can operate to remove edema from the damaged cardiac tissue 7, thus preserving cardiac function to increase the probability of recovery and survival in a more physiologically preserved state.

[0054] Turning to FIG. 10, sub-atmospheric pressure may be delivered under the cover 50 by cooperation between the cover 50 and the tube 20. Specifically, the flexible overlay cover 40 (or self-adhesive flexible overlay cover 50) may include a passthrough 52 through which the distal end 22 of the tube 20 passes to provide gaseous communication between the tube 20 and the space under the flexible overlay cover 40 over the damaged cardiac tissue.

[0055] In another of its aspects, the present invention also provides a method for treating damaged cardiac tissue using sub-atmospheric pressure with, by way of example, the devices illustrated in FIGS. 1-4. In particular, the method may comprise locating a porous material 10 proximate the damaged cardiac tissue 7 to provide gaseous communication between one or more pores of the porous material 10 and the damaged cardiac tissue 7. The porous material 10 may be sealed in situ proximate the damaged cardiac tissue 7 to provide a region about the damaged cardiac tissue 7 for maintaining sub-atmospheric pressure at the damaged cardiac tissue 7. In this regard, the muscles 3, and bone 4 may be loosely re-approximated over top of the porous material 10 with the tube 20 exiting through the skin 1 and subcutaneous tissue 2 and the skin 1 and subcutaneous tissue 2 sutured closed. A further airtight dressing may optionally be placed over the suture site to promote an airtight seal. The porous material 10 may be operably connected with a vacuum source 30 for producing sub-atmospheric pressure at the damaged cardiac tissue 7, and the vacuum source 30 activated to provide sub-atmospheric pressure at the damaged cardiac tissue 7. For example, the sub-atmospheric pressure may be maintained at about 25 to 125 mm Hg below atmospheric pressure. The sub-atmospheric pressure may be maintained at the damaged cardiac tissue 7 for a time sufficient to decrease edema at the damaged cardiac tissue 7. In addition, the sub-atmospheric pressure may be maintained at the damaged cardiac tissue 7 for a time sufficient to prepare the cardiac tissue 7 to achieve a stage of healing and diminution of edema and inflammatory mediators or amplifiers. The method may be used for at least 2 hours, or can be used for many days. At the end of the vacuum treatment, the sutures 8 may be removed and the skin 1, subcutaneous tissue 2, muscles 3 and bone 4 re-opened. The porous material 10 may then be removed and the skin 1, subcutaneous tissue 2, and/or muscles 3 re-sutured closed.

[0056] The method may also include locating an overlay cover 40, 50, such as a bio-incorporable cover 40, 50, over the damaged cardiac tissue 7 and sealing the overlay cover 40, 50 to tissue proximate the damaged cardiac tissue 7 for maintaining sub-atmospheric pressure at the damaged cardiac tissue 7. The step of sealing the overlay cover 40, 50 to tissue surrounding the damaged cardiac tissue 7 may comprise adhesively sealing and adhering the overlay cover 40, 50 to tissue surrounding the damaged cardiac tissue 7. The overlay cover 50 may be provided in the form of a self-adhesive sheet 50 which may be located over the damaged cardiac tissue 7. In such a case, the step of sealing the overlay cover 50 may include adhesively sealing and adhering the self-adhesive overlay cover 50 to non-damaged cardiac tissue 6 surrounding the damaged cardiac tissue 7 to form a seal between the overlay cover 50 and the non-damaged cardiac tissue 6 surrounding the damaged cardiac tissue 7. In addition, the step of operably connecting a vacuum source 30 in gaseous communication with the porous material 10 may comprise connecting the vacuum source 30 to the tube 20 which attaches to the vacuum port 42 of the cover 140 FIG. 11.

[0057] In still another aspect of the present invention, in addition to injured tissues and organs, the devices and methods may also be used to increase the size and function of diseased or damaged organs. For example, the size of a partially functioning kidney may be increased to a size sufficient to return the total filtering capacity to normal levels, FIGS. 12-14, such as the increase in size of the remaining kidney 301 as is observed in patients who only have one functioning kidney 301. In such a situation, a rigid or semi-rigid bi-valved enclosure 304 with an opening 305 for the vascular pedicle may be placed around the kidney 301. When the bi-valved enclosure 304 is closed, the area where the two halves meet creates an air tight seal. The vascular pedicle enters (artery 302) and exits (vein 303) through the opening 305. Fibrin glue 306 or other biocompatible sealant may be placed around the artery 302 and vein 303 at the site of the opening 305 to create an airtight seal. The enclosure 304 may include a second opening 305 or a nipple 308. A tube 309 may be inserted through the second opening 305 or attached to the nipple 308. The tube 309 may exit through the skin, be connected to a collection vessel, and then connected to a vacuum source. A controlled vacuum of up to 125 mm Hg sub-atmospheric pressure may be applied either intermittently, with an on time of up to five minutes and an off time of up to 10 minutes. Alternatively, the vacuum may be applied in a periodic or cyclical manner, such as a sine wave, in which the absolute value of the lower (closest to atmospheric pressure) values of the applied vacuum are less than the diastolic blood pressure to allow blood to flow out of the treated organ. The time in which the applied vacuum is greater (in absolute value) than the diastolic blood pressure may be up to five minutes, with the time in which the applied vacuum is lower (in absolute value) than the diastolic blood pressure may be up to ten minutes. The technique is continued until the treated organ has either reached the desired level of function or fills the container. As an additional example, this device and technique may similarly be used on lobes of the liver or for increasing the size of the pancreas.

EXAMPLES

Example 1

[0058] The porcine heart has anatomy similar to that of humans with the main vasculature consisting of the right and left coronary arteries. The left main coronary artery splits into the circumflex coronary artery and the left anterior descending (LAD) coronary artery. The LAD runs down along the anterior septum and perfuses the anterior portion of the left ventricle with diagonal branches. For these studies, a porcine model of ischemia-reperfusion was used that included the temporary ligation of 2-3 diagonal branches of the LAD in order to create an ischemic area on the anterior portion of the heart. These coronary arteries were occluded for 75 minutes and then reperfused for 3 hours to allow for ischemia/reperfusion injury to develop. The negative pressure therapy was applied only during the reperfusion phase of the experiments to simulate a clinically relevant treatment window.

[0059] To begin the study, the animals were sedated and transported to the operating room. The first 13 animals had the heart exposed through a thoracotomy, all subsequent animals had the heart exposed through a sternotomy. The 2-3 diagonal branches of the LAD were ligated (occluded with suture) in order to create an ischemic area on the anterior portion of the heart. These coronary arteries were occluded for 75 minutes and then reperfused for 3 hours to allow for reperfusion injury to develop. The negative pressure therapy was applied only during the reperfusion phase of the experiments to simulate a clinically relevant treatment window. Five control animals were created from the first 13 animals of the study.

[0060] Following successful completion of control animals to validate the study design, the subsequent 5 successful (sternotomy) animals had negative pressure therapy treatment to the ischemic area of the heart for 3 hours during the reperfusion time. For the first 5 successfully treated animals, the vacuum dressing included use of a polyvinyl alcohol porous material (Versafoam, KCl, San Antonio Tex.), cut to approximately 1 mm thickness and trimmed to match the ischemic area. The evacuation tube was either embedded into a slit cut into the porous material (2 animals), or was sutured to the outer surface of the porous material (3 animals). This vacuum dressing was then covered with a biologically derived overlay cover. These biological coverings included: 1 animal treated with EZ DERM (Non-perforated porcine biosynthetic wound dressing, Brennen Medical, St. Paul, Minn.); 1 animal treated with bovine pericardium; and 3 animals treated with AlloDerm (human dermis) (LifeCell). The overlay covers were attached to the heart by three means: suturing, fibrin glue, and self sealing due to a relatively large apron of the cover material around the periphery of the vacuum dressing. The evacuation tube exited from under the edge of the apron of the overlay covers. The fibrin glue was used in conjunction with suturing and also with spot sealing for the self sealing application (at wrinkles, where the evacuation tube exited, etc.). Negative pressure of 125 mm Hg (i.e., 125 mm Hg below atmospheric) was then applied for 3 hours during the reperfusion period using The V.A.C., Model 30015B, Kinetic Concepts, Inc., San Antonio, Tex.

[0061] To determine the effects of ischemia/reperfusion, the sutures were re-tied at the end of the 3 hour reperfusion period. Blue dye (patent blue, Sigma-Aldrich Inc, St. Louis, Mo.) was injected into the right atrium. This stained the areas of the heart that were normally perfused. The left ventricle was dissected free from the rest of the heart and weighed (LV in Table). The area of ischemia (non-blue area) was further dissected from the left ventricle. The blue area of the left ventricle was then weighed (Blue in Table). The ischemic area (non-blue tissue) was then stained with a dye (2,3,5-triphenyltetrazolium chloride, Sigma-Aldrich Inc., St Louis Mo.) which stains live cells red. The red areas were dissected from the area of ischemia and were weighed (Red in Table), leaving areas of pale dead tissue (area of necrosisAN in Table), and these pale tissue samples were weighed (Pale in Table). The combined Red and Pale areas constitute the area at risk (AAR in Table). The AN/AAR is the size of the infarct (percent of tissue that died during the ischemia/reperfusion time periods).

[0062] The results for the 5 control animals were:

TABLE-US-00001 TABLE 1 Control Animals Pale AAR/LV AN/AAR Blue Red (AN) LV AAR (%) (%) Animal 1 75.6 5.85 2.18 83.63 8.03 9.60 27.15 Animal 2 90.5 10.63 2.44 103.57 13.07 12.62 18.67 Animal 3 85.39 12.16 4.26 101.81 16.42 16.13 25.94 Animal 4 92.45 8.17 3.47 104.09 11.64 11.18 29.81 Animal 5 81.24 9.86 4.34 95.44 14.20 14.88 30.56 Mean 97.71 12.67 12.88 26.43 Std 8.59 3.13 2.66 4.73 Dev N 5.00 5.00 5.00 5.00 Std 3.84 1.40 1.19 2.12 Err

[0063] The results for the 5 treated animals were:

TABLE-US-00002 TABLE 2 125 mm Hg Treated Animals AAR/LV AN/AAR Group Blue Red Pale LV AAR (%) (%) Animal 1 73.06 10.31 1.23 84.60 11.54 13.64 10.66 Animal 2 73.2 5.9 0.61 79.71 6.51 8.17 9.37 Animal 3 75 11.15 2.05 88.20 13.20 14.97 15.53 Animal 4 54.1 4.85 0.52 59.47 5.37 9.03 9.68 Animal 5 62.12 8.63 1.42 72.17 10.05 13.93 14.13 Mean 76.83 9.33 11.95 11.87 Std 11.41 3.32 3.11 2.78 Dev N 5.00 5.00 5.00 5.00 Std 5.10 1.48 1.39 1.24 Err

[0064] Thus, the mean sizes of the infarct (AN/AAR; percent of tissue that died during the ischemia/reperfusion time period) for the control and treated animals were:

Control 26.43+/2.12% (mean+/SEM) (n=5)

Treated 11.87+/1.24% (mean+/SEM) (n=5),

with T-test results of P<0.001 for infarct size and P<0.625 for area at risk.

Example 2

[0065] Another experiment was conducted using 50 mm Hg vacuum for treatment for comparison to original control animals from Example 1 above. The surgical technique in this experiment was similar to that used for those of Example 1. These animals were sedated and prepped for surgery. The heart was exposed through a midline sternotomy. Branches of the left anterior descending artery were ligated for 75 minutes. A polyvinyl alcohol vacuum dressing was placed over the ischemic area and an AlloDerm cover was placed over the vacuum dressing and sealed into place with a combination of sutures and fibrin glue. Negative pressure of 50 mm Hg was applied for 3 hours. At the end of this time the heart was stained for area of risk, removed and then counter stained for area of necrosis. The infarct size results for these five, 50 mm Hg negative pressure therapy animals were significantly smaller (P<0.001) than for the control animals. The infarct size for the 50 mm Hg treated animals was smaller than the infarct size for the 125 mm Hg treated animals, but was not significantly smaller.

TABLE-US-00003 Group AAR/LV (%) AN/AAR Control 12.9 1.2 26.4 2.1 50 mmHg negative 11.8 2.0 9.3 1.8** pressure 125 mmHg negative 11.9 1.4 11.9 1.2** pressure **p < 0.001 compared to Control animals

[0066] The mean arterial pressure and heart rate of animals in all three groups (control, 125 mm Hg, 50 mm Hg) were comparable during the course of these experiments.

[0067] Fifteen micron neutron-activated microspheres (BioPAL, Inc, Worcester, Mass.) were injected into the left atrium at baseline, end of ischemia, 30 minutes into reperfusion and at 180 minutes of reperfusion (end of the experiment). A reference sample of arterial blood was simultaneously drawn from the femoral artery at a rate of 7 mL per minute for ninety seconds. Following infarct sizing procedures, tissue samples from the non-ischemic (blue tissue), ischemic non-necrotic (red tissue), and ischemic necrotic areas (pale tissue) were collected and sent to the manufacturer for blood flow analysis (BioPAL, Inc., Worchester, Mass.). Blood flow was calculated as [(FRCPMT)/CPMR)/tissue weight in grams, where FR=reference sample flow rate (7 mL/min), CPMT=counts per minute in tissue samples and CPMR=counts per minute in the reference blood sample. Blood flow is reported as mL/min/gram tissue.

[0068] Analysis of blood flow reveals that both treated groups had similar baseline blood flows in all 3 regions. In the normally perfused non-ischemic zone, blood flow remained relatively constant throughout the experiment with no significant group or time related differences. (Table 3) In the ischemic, non-necrotic (red) and ischemic, necrotic zones (pale), ischemia was characterized by an equivalent and nearly complete loss of blood flow among all three groups. These zones also exhibited normal reactive hyperemia (30 minutes after reperfusion), and blood flow that returned approximated baseline flow levels by the end of the 3 hour reperfusion time. (Table 4).

TABLE-US-00004 TABLE 3 Blood flow (ml/minute/gram tissue) from microsphere analysis Baseline Control 125 mm Hg 50 mm Hg Animal blue Red Pale blue Red Pale blue Red Pale 1 0.36 0.328 0.333 0.596 1.1 0.77 2 1.072 0.709 0.716 0.308 0.401 0.448 0.474 0.321 0.551 3 0.378 0.347 0.505 0.392 0.411 0.353 0.531 0.444 0.422 4 0.577 0.729 0.599 0.643 1.32 0.82 0.625 0.629 0.699 5 0.376 0.495 0.412 0.423 0.687 0.482 0.393 0.57 0.596 Mean 0.603 0.57 0.558 0.4252 0.629 0.487 0.524 0.613 0.608 SD 0.33 0.18 0.13 0.13 0.41 0.20 0.09 0.30 0.13 N 4 4 4 5 5 5 5 5 5 SEM 0.16 0.09 0.07 0.06 0.18 0.09 0.04 0.13 0.06 During Occlusion Control 125 mm Hg 50 mm Hg Animal Blue Red pale blue Red pale blue Red pale 1 0.345 0.065 0.012 0.387 0.056 0.025 2 1.031 0.073 0.0255 0.335 0.064 0.029 0.352 0.008 0.029 3 0.3 0.016 0.022 1.196 0.06 0.051 0.714 0.024 0.041 4 0.428 0.129 0.017 0.454 0.084 0.071 0.494 0.038 0.035 5 0.4 0.024 0.011 0.509 0.054 0.029 0.441 0.037 0.1 Mean 0.540 0.061 0.0189 0.568 0.065 0.038 0.478 0.033 0.046 SD 0.33 0.05 0.01 0.36 0.01 0.02 0.14 0.02 0.03 N 4 4 4 5 5 5 5 5 5 SEM 0.17 0.03 0.00 0.16 0.01 0.01 0.06 0.01 0.01 Reperfusion 30 minutes Control 125 mm Hg 50 mm Hg Animal blue red pale blue Red pale blue red pale 1 0.379 1.341 1.022 0.441 1.355 2.361 2 1.102 1.522 1.872 0.37 0.559 0.692 0.402 0.628 0.708 3 0.348 0.54 0.286 0.298 0.878 0.6 0.741 1.699 1.626 4 0.439 1.054 1.225 1.439 0.909 1.288 0.603 1.126 1.477 5 0.496 1.272 1.4 0.676 1.866 1.147 Mean 0.596 1.097 1.196 0.622 0.922 0.901 0.573 1.335 1.464 SD 0.34 0.42 0.67 0.55 0.32 0.32 0.15 0.49 0.61 N 4 4 4 4 4 4 5 5 5 SEM 0.17 0.21 0.33 0.27 0.16 0.16 0.07 0.22 0.27 Reperfusion 180 minutes Control 125 mm Hg 50 mm Hg Animal blue red pale blue Red Pale blue red Pale 1 0.404 0.367 0.795 0.467 0.385 0.837 2 1.102 1.522 1.872 0.291 0.365 0.6 0.593 0.186 0.649 3 0.348 0.54 0.286 0.38 0.303 0.515 0.804 0.649 0.699 4 0.439 1.054 1.225 0.513 0.449 0.845 0.912 0.803 0.946 5 0.496 1.272 1.4 0.53 0.477 0.76 0.483 0.471 0.495 Mean 0.596 1.097 1.196 0.424 0.392 0.703 0.652 0.499 0.725 SD 0.34 0.42 0.67 0.10 0.07 0.14 0.20 0.24 0.17 N 4 4 4 5 5 5 5 5 5 SEM 0.17 0.21 0.33 0.04 0.03 0.06 0.09 0.11 0.08

TABLE-US-00005 TABLE 4 Regional Myocardial blood flow (mL/min/100 g tissue) Control 50 mm Hg 125 mm Hg Blue Red Pale Blue Red Pale Blue Red Pale Baseline 0.60 0.16 0.57 0.09.sup. 0.56 0.07 0.52 0.04 0.61 0.13.sup. 0.61 0.06 0.43 0.06 0.63 0.18.sup. 0.49 0.09 Occlusion 0.54 0.17 0.06 0.03.sup. .sup.0.02 0.00.sup. 0.48 0.06 0.03 0.01.sup. .sup.0.05 0.01.sup. 0.57 0.16 0.07 0.01.sup. 0.04 0.01 R30 0.60 0.17 1.10 0.21.sup. .sup.1.2 0.33.sup. 0.57 0.07 1.33 0.22.sup. .sup.1.46 0.27*.sup. 0.62 0.27 0.92 0.16.sup. 0.90 0.16 R180 0.41 0.04 1.39 0.35.sup. 0.95 0.16 0.65 0.09 0.50 0.11.sup. 0.73 0.08 0.42 0.04 0.39 0.03.sup. 0.70 0.06* Regional myocardial blood flow was determined in 3 regions of the heart: 1)non-ischemic left ventricle; 2) ischemic, non-necrotic left ventricle; 3) necrotic left ventricle. *p < 0.05 vs Control within a time period and within tissue area; .sup.p < 0.05 vs. Baseline within group and tissue area.

Example 3

[0069] A subsequent study was performed to examine resorbable vacuum dressings and overlay covers. One animal was sedated, prepared for surgery as described, and the heart exposed through a mid-line sternotomy. Branches of the LAD were ligated for 90 minutes. The dressing was prepared by freeze drying. A solution of chitosan (1.33% weight/volume in 2% acetic acid, 20 ml total volume) was poured into an appropriately sized mold. The solution was frozen for 2 hours at 70 C., then transferred to the lyophylizer for 24 hours. The dressing was cross-linked by 2.5% glutaraldehyde vapor for 12 hours to provide a porous material. The overlay cover was an electrospun mixture of Type I collagen and poly 1,8-octanediol citrate (POC) (80%:20% weight/weight). The solution concentration was 15% dissolved in hexafluoro-20proponal (HFIP) with a total volume of 9.5 ml. The solution was ejected from a syringe through an 18 gauge needle at a flow rate of 3 ml/hour. The voltage was 25 KV with a working distance of 25 cm. The film was then heat polymerized at 80 C. for 48 hours and cross-linked in 2.5% glutaraldehyde vapor for 24 hours. The overlay cover was able to maintain the vacuum for the duration of the experiment. However, the vacuum dressing did not distribute the vacuum equally throughout the dressing due to collapse and flow of the material under vacuum.

Example 4

[0070] A further study was performed to test variations of the overlay cover. Three animals were sedated and the heart exposed through a midline sternotomy. No infarct was created in this study of materials. The overlay cover was created similar to Example 3, but with variations, including changes in voltage, flow rate, and concentration of glutaraldehyde vapor for cross-linking. For these animals, the porous material vacuum dressing was formed from a solution of 80% Type I collagen/20% POC, 12% total concentration in 8.5 ml HFIP was used. The flow rate was 2 ml/hour, with the fluid ejected through an 18 gauge needle at 35 KV with a working distance of 25 cm. The film was heat polymerized at 80 C. for 48 hours, then cross-linked with exposure to 5% glutaraldehyde vapor for 24 hours. The evacuation tube was sutured to a thin polyvinyl alcohol dressing. The dressing was placed over a portion of the left ventricle and tacked in place with 2-4 sutures. The overlay cover was placed over the dressing and fibrin glue was placed around the edges of the overlay cover to insure a vacuum seal. 50 mm Hg was applied continuously to the dressing. For two animals a small air leak developed after approximately 2.5 hours, the source of the leak was not identified despite a diligent search for the source. The source of the leak could have been at the site of a wrinkle in the overlay cover, a tail of the suture material could have punctured a hole in the overlay cover, fluid collecting in the pericardial sack could have floated a small portion of the cover off the heart tissue, etc. For the third animal, the negative pressure was maintained for the duration of the study (4 hours application of negative pressure).

Example 5

[0071] Two animals were used to test the dressing. The surgical technique was similar to that used above. These animals were sedated, prepped for surgery and the heart exposed through an midline sternotomy. Branches of the left anterior descending artery were ligated for 75 minutes. A dressing was made by casting polycaprolactone (PCL). Polycaprolactone was mixed with sodium chloride (1 part caprolactone to 10 parts sodium chloride) and placed in a sufficient volume of chloroform to dissolve the components. 8 ml of the solution was poured into an appropriately sized and shaped container and allowed to dry for twelve hours. The sodium chloride was then leached out in water for 24 hours. The dressing was cut to the size of the ischemic area. The evacuation tube was sutured to the dressing and the dressing placed over the ischemic area and tacked into place. At the end of the 75 minutes of ischemia the tissue was reperfused. The dressing was covered with AlloDerm and fibrin glue was placed around the edges of the AlloDerm. 50 mm Hg vacuum was applied for 3 hours. At the end of this time the heart was stained for area of risk, removed and then counter stained for area of necrosis as described for Examples 1 and 2. For the first animal, the area at risk (ischemic area, AAR) was fairly small at 7.9% of the left ventricle (LV). The infarct size (area of necrosis divided by area at risk (AN/AAR100%) was very small at 2.6% of the area at risk. For the second animal, the area at risk was larger at 14.3% (AAR/LV), with an infarct size (AN/AAR) of 11.52%.

[0072] These and other advantages of the present invention will be apparent to those skilled in the art from the foregoing specification. Accordingly, it will be recognized by those skilled in the art that changes or modifications may be made to the above-described embodiments without departing from the broad inventive concepts of the invention. It should therefore be understood that this invention is not limited to the particular embodiments described herein, but is intended to include all changes and modifications that are within the scope and spirit of the invention as set forth in the claims.