Classifications

• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M25/00—Catheters; Hollow probes
  • A61M25/10—Balloon catheters
  • A61M25/104—Balloon catheters used for angioplasty
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M37/00—Other apparatus for introducing media into the body; Percutany, i.e. introducing medicines into the body by diffusion through the skin
  • A61M37/0092—Other apparatus for introducing media into the body; Percutany, i.e. introducing medicines into the body by diffusion through the skin using ultrasonic, sonic or infrasonic vibrations, e.g. phonophoresis
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
  • A61N1/00—Electrotherapy; Circuits therefor
  • A61N1/02—Details
  • A61N1/04—Electrodes
  • A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
  • A61N1/00—Electrotherapy; Circuits therefor
  • A61N1/18—Applying electric currents by contact electrodes
  • A61N1/20—Applying electric currents by contact electrodes continuous direct currents
  • A61N1/30—Apparatus for iontophoresis, i.e. transfer of media in ionic state by an electromotoric force into the body, or cataphoresis
  • A61N1/303—Constructional details
  • A61N1/306—Arrangements where at least part of the apparatus is introduced into the body
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
  • A61N1/00—Electrotherapy; Circuits therefor
  • A61N1/18—Applying electric currents by contact electrodes
  • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
  • A61N1/325—Applying electric currents by contact electrodes alternating or intermittent currents for iontophoresis, i.e. transfer of media in ionic state by an electromotoric force into the body
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M25/00—Catheters; Hollow probes
  • A61M25/0043—Catheters; Hollow probes characterised by structural features
  • A61M2025/0057—Catheters delivering medicament other than through a conventional lumen, e.g. porous walls or hydrogel coatings
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M25/00—Catheters; Hollow probes
  • A61M25/10—Balloon catheters
  • A61M25/1011—Multiple balloon catheters
  • A61M2025/1013—Multiple balloon catheters with concentrically mounted balloons, e.g. being independently inflatable
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M25/00—Catheters; Hollow probes
  • A61M25/10—Balloon catheters
  • A61M2025/1043—Balloon catheters with special features or adapted for special applications
  • A61M2025/105—Balloon catheters with special features or adapted for special applications having a balloon suitable for drug delivery, e.g. by using holes for delivery, drug coating or membranes
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
  • A61N1/00—Electrotherapy; Circuits therefor
  • A61N1/02—Details
  • A61N1/04—Electrodes
  • A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
  • A61N1/056—Transvascular endocardial electrode systems
  • A61N2001/0585—Coronary sinus electrodes

Definitions

• the present invention relates to a drug delivery apparatus and method for selectively and locally delivering a drug to internal body tissue. More particularly, the present invention relates to a catheter device including a polymer matrix containing a drug and transport means for actively transporting the drug from the polymer matrix to the internal body tissue.
• localized internal delivery devices avoid the high dosage levels associated with systemic delivery which can result in adverse side effects.
• Systemic delivery also fails to concentrate the therapeutic agents in the local area where they are most effective.
• the total quantity of drug used may be significantly reduced which also reduces the cost of therapy.
• localized drug delivery may also allow the use of therapeutic agents which, although very effective, have previously been considered too toxic or non-specific to administer systemically.
• PTCA percutaneous transluminal coronary angioplasty
• catheters are inserted into the cardiovascular system under local anesthesia and an expandable balloon portion is then inflated to compress the atherosclerosis and dilate the lumen of the artery.
• high restenosis rates (reported to be as high as 47%) continue to be a major problem.
• Various techniques have been tried to treat stenosed vessels including the use of lasers, application of heat and the use of intravascular stents. However, many of these are still under investigation with mixed results, while others have generally not been successful.
• the ability to administer a drug locally to the dilated portion of the artery in PTCA procedures, without significantly affecting other tissues, would greatly enhance the ability to address the restenosis problem.
• a second example of specific application for a local drug delivery system for delivering a drug to an internal body tissue is in the treatment of cancerous tumors or the like.
• an objective is to administer the cancer drug so that it localizes, as much as possible, in the tumor itself.
• Such drugs are commonly administered systemically through the blood stream.
• Various means are then utilized for causing the drug to localize in the cancer tumor. Nevertheless, significant portions of the drug still circulate through the blood stream, thereby affecting non-cancerous tissue, producing undesirable side effects, and limiting the dosages of the drug which can be safely administered.
• Double balloon catheters have been used to administer agents to the area confined by the balloons in a vessel or other body passageway. That system, however, has the disadvantage in that drugs may be lost through communicating vessels between the balloons.
• a perforated balloon has been used to deliver drug solutions under pressure across a porous balloon wall and directly into a hollow organ.
• catheter-based local drug delivery systems are somewhat effective, they are typically designed to deliver therapeutic agents in solution. That limitation is the source of several disadvantages.
• the desired therapeutic agent must be readily soluble in an appropriate solvent. Many drugs are not, however, easily solubilized in aqueous-based solvents.
• the catheters must be equipped with conduits to introduce and possibly evacuate the liquid solution, as well as a terminal drug reservoir.
• Such devices typically use inflatable balloons which either act as drug reservoirs or restrict drug movement to a specific segment of the vessel or hollow organ.
• one or more conduits must also be provided to inflate and deflate the catheter balloon. Multiple conduits such as those described above not only add to the complexity and cost of the catheter, but also increase its profile, thereby limiting the applications for which it can be used.
• the liquid drug solution must be prepared and introduced into the catheter by the physician. Such procedures add time, complication and expense to the use of these devices and are also more likely to result in the administration of inaccurate dosages.
• United States Patent No. 5,102,402 to Dror et al. discloses the use of drugs contained in micro- capsules located on the outer surface of a balloon catheter. The capsules are ruptured using sonic energy. Upon rupturing, the capsules deliver the drug internally. This patent does not, however, disclose the use of phonophoresis to actively transport the drugs into the surrounding tissue. Instead, the drug is delivered through passive diffusion, thereby limiting its penetration.
• an apparatus and method for active delivery of a drug or combination of drugs selectively and locally to an internal body tissue using a polymer matrix incorporated into a catheter-based delivery system.
• the invention involves an apparatus and method for active delivery of a drug or combination of drugs substantially transversely to the longitudinal axis of a body passageway such as blood vessel, urinary tract, intestinal tract, reproductive tract, etc., to treat a localized region of the passageway itself or to treat a localized region or tissue located adjacent to the passageway.
• the invention also involves an apparatus and method for active delivery of a drug or combination of drugs directly to an internal body tissue.
• the apparatus includes a flexible member adapted for insertion into the body passageway or tissue and a drug delivery means connected with the flexible member for delivering the drug to or through a local area of the passageway wall or tissue.
• the drug delivery means includes a drug incorporated into a polymer matrix.
• transport means associated with the drug delivery means for actively transporting the drug out of the polymer matrix to the area to be treated.
• the transport means is typically iontophoresis or phonophoresis.
• the method of the present invention involves positioning a drug delivery member, including a polymer matrix containing a drug, in a body passageway such that the delivery member traverses the desired localized area of administration.
• the method for delivering a drug to an internal body tissue involves positioning the drug delivery component at a target area of an internal body tissue and actively transporting the selected drug from the polymer matrix into the internal body tissue target area.
• Polymer matrixes incorporating drugs have been previously employed as implantable slow sustained release devices.
• the present invention adds an active transport means, i.e., either iontophoresis or phonophoresis, to rapidly and effectively transport the drugs from the polymer matrix into the targeted area.
• the present invention also solves many of the disadvantages associated with known catheter-based local internal drug delivery systems. Because the drug is not in liquid form, the need for conduits to deliver and evacuate the drug solution is also eliminated. That can help limit the profile, and cost, of the catheter.
• the matrix is pre-loaded with a known quantity of medication and delivered by an active transport means such as iontophoresis or phonophoresis which allows for precise and controlled drug delivery.
• the polymer matrix also eliminates the chance of leakage of the drug solution and the resulting problems associated with those occurrences.
• the catheter can be inserted without any need for preparing, filling or circulating a drug solution through the catheter, also saving time and simplifying usage.
• FIG. 1 is a fragmentary view, partially in section, of a first embodiment of the drug delivery apparatus of the present invention in the form of a catheter with a polymer matrix and transport means before expansion.
• Figure 2 is a fragmentary view, partially in section, of the drug delivery apparatus of Figure 1 with the transport means located within the polymer matrix.
• Figure 3 is a fragmentary view, partially in section, of the apparatus of Figure 1, after removal of the transport means from the polymer matrix.
• Figure 4 is a partial cross-section of a further embodiment of the drug delivery apparatus of the present invention.
• Figure 5 is a partial cross-section of the embodiment of Figure 4 with the polymer matrix expanded.
• Figure 6 is a partial cross-section of the embodiment of Figures 4 and 5, with the catheter prepared for removal.
• Figure 7A is a schematic representation of a manually-loaded wire basket electrode for use in the present invention.
• Figure 7B is a schematic representation of the manually-loaded wire basket electrode of Figure 7A in its expanded state.
• Figure 8A is a partial cross-sectional view of a further embodiment of the drug delivery apparatus of the present invention incorporating a balloon to expand the polymer matrix and an expandable electrode placed between the balloon and the polymer matrix.
• Figure 8B is a partial cross-sectional view of the catheter of Figure 8A in its expanded state.
• Figure 9A is a partial cross-sectional view of a further embodiment of the drug delivery apparatus of the present invention incorporating a balloon for expansion and a central electrode.
• Figure 9B is a partial cross-sectional view of the catheter of Figure 9A in its expanded state.
• Figure 10 is a partial cross-sectional view of a further embodiment of the drug delivery apparatus of the present invention incorporating a balloon for expansion and a transducer for phonophoresis.
• Figure 11 is a partial cross-sectional view of a further embodiment of the drug delivery apparatus of the present invention designed for use in internal tissue where expansion of the polymer matrix is not needed to provide intimate contact.
• Figure 12A is a view of a further embodiment of the drug delivery apparatus of the present invention incorporating a movable sheath for protection of the polymer matrix.
• Figure 12B is a view of the catheter of Figure
• Figure 13 is a view of a further embodiment of the drug delivery apparatus of the present invention incorporating a porous outer membrane for protection of the polymer matrix.
• Figures 1-13 illustrate the preferred and various alternate designs of the drug delivery apparatus in accordance with the present invention.
• this apparatus provides a means and a system for delivering a drug or combination of drugs to or through a localized area of a passageway to treat the localized area of the passageway or to treat a localized area of tissue located adjacent to the passageway, with minimal, if any, undesirable effect on other body tissue.
• catheter as used in the present application is intended to broadly include any medical device designed for insertion into a body passageway to permit injection or withdrawal of fluids, to keep a passage open or for any other purpose.
• the drug delivery apparatus of the present invention has applicability for use with any body passageways including, among others, blood vessels, urinary tract, intestinal tract, reproductive tract, respiratory tract and the like. Many of the embodiments are also capable of delivering a drug or combination of drugs to a localized area of an internal body tissue.
• the apparatus includes a flexible catheter connected to a drug delivery component having a polymer matrix surrounding a transport means.
• the transport means is used to actively transport the drug from the polymer matrix to an internal body tissue target area.
• Catheters are commonly used in percutaneous transluminal coronary angioplasty (PTCA) procedures to dilate stenosed blood vessels or arteries. These include "over-the-wire" catheters of the type illustrated generally in U.S. Patent No.
• PTCA percutaneous transluminal coronary angioplasty
• a dilatation catheter is advanced along an artery to the desired position in the arterial system.
• the catheter includes an inflatable balloon at its distal end and means for inflating the balloon.
• the balloon is inflated to compress the atherosclerosis and expand the artery in a direction generally perpendicular to its wall, thereby dilating the lumen of the artery.
• the balloon is deflated and the catheter withdrawn.
• restenosis the tendency of the dilated artery to close
• Restenosis can include abrupt reclosure resulting from thrombotic occlusion, vasospasms, or the like as well as the more common occurrence of gradual restenosis.
• a drug referred to as a fixation solution or a fixative is delivered locally to the dilated portion of the vessel to render the vessel wall biologically inert to prevent or reduce reactions that lead to reclosure. Because of the nature of the fixative and its ability to inactivate living cells and render the tissue in which it comes into contact biologically inert, it is essential that such fixative be exposed only to that portion of the arterial wall which has been dilated.
• a preferred method and apparatus for delivering the fixative locally to the dilated vessel is via a catheter modified according to the present invention.
• the catheter that delivers the drug may be the same catheter that dilates the vessel, thus combining both functions in one catheter.
• a vessel may be dilated first with a catheter designed specifically for dilation, followed by insertion of a second catheter for drug delivery.
• Modified catheters useful for either approach is illustrated in Figures 1-3, 8 or 9, all of which are described in detail below.
• Figure 1 illustrates the distal end of a catheter.
• the catheter includes an elongated, flexible catheter body 11, a drug delivery means in the form of a drug-impregnated polymer matrix 12 positioned in the catheter body 11 near its distal end.
• impermeable end caps 17 are located on either end of the substantially cylindrical polymer matrix 12 to prevent movement of the drug in the matrix 12 longitudinally along the catheter body 11.
• the end caps 17 are, however, optional and may be added or removed as desired depending on the extent of leakage in the axial direction during drug transport and any undesirable effects that the leakage may have on the patient.
• An electrode passageway 14 extends along the catheter body 11 on either side of the polymer matrix 12.
• a wire 16 is attached to the electrode 18 which is positioned in the distal end of passageway 14.
• the wire 16 extends from the proximal end of the catheter body 11 to its distal end where it is attached to electrode 18.
• the polymer matrix material used as the drug reservoir should be a compliant and expandable material that is, ideally, also non-compressible or minimally compressible.
• the material must be compliant and expandable to allow sufficient expansion of the polymer matrix material by the expansion means, whether the expansion means is an electrode 18 as in Figure 1, wire basket 56 as in Figure 5, wire basket 70 as in Figure 7A or balloon 86 in Figure 8.
• the compressibility of the material is preferably limited to maximize the diameter of the catheter when the polymer matrix material is expanded, thus ensuring intimate contact between the polymer matrix and target tissue to enhance drug transfer.
• the polymer matrix material could be compressible, provided that the expansion means is designed to ensure intimate contact in spite of the compressibility of the polymer matrix material.
• the polymer matrix material need not be expandable or non-compressible and may, in fact , be rigid if desired.
• polymer matrix includes synthetic polymers in the form of hydrogels or other porous or drug-permeable configurations or morphologies, such as polyvinyl alcohol, polyvinylpyrrolidone and polyacrylamide, polyethylene oxide, poly(2-hydroxy ethyl methacrylate) ; natural polymers such as gums and starches; synthetic elastomers such as silicone rubber, polyurethane rubber; and natural rubbers.
• the above examples are provided for reference only, and the range of suitable polymer matrix materials should not be construed as limited to those materials listed above.
• the polymer matrix material can also be hydrophilic or hydrophobic, provided it meets the physical characteristics described above.
• Drugs may be incorporated into the polymer matrix material by a variety of methods.
• the drug can be incorporated into the material as the polymer solution or dispersion is formed into the preferred annular shape; it can be added to the polymer matrix material after formation into the desired shape either passively or actively (through, for example, such methods as iontophoresis); the drug can be dissolved in a solvent (e.g., water, propylene, glycol, etc.) and the resulting solution can be incorporated into the polymer matrix material; or the drug molecules can be incorporated directly into the polymer matrix material.
• Figure 2 illustrates the drug delivery apparatus of Figure 1 with the polymer matrix 12 in its expanded state within an arterial vessel with walls 15.
• the catheter including the catheter body 11 and polymer matrix 12 is advanced to the desired position in the arterial system in which the polymer matrix 12 traverses or crosses the stenotic lesion.
• the matrix 12 is then expanded by pulling the electrode 18 into the interior chamber 13 of the polymer matrix 12.
• Wire 16 is preferably attached to a handle (not shown) at the proximal end of the catheter to allow electrode 18 to be pulled into the matrix 12.
• wire 16 is used to move electrode 18 into position in the matrix 12 (thereby expanding the matrix) as well as providing current to electrode 18 after the electrode is in place.
• the outer surfaces of the polymer matrix 12 press outwardly against the inner surfaces of the vessel wall 15 to expand or dilate the vessel in the area of the stenotic lesion.
• the fixative or other drug in the matrix 12 is then transported into the surrounding tissue using iontophoresis.
• catheters according to the present invention may be used to perform dilation of the vessel as well as deliver the fixative or other drug to the targeted tissue.
• the preferred drug transport means is iontophoresis, which uses an electrical potential or current to drive ionic fixatives or drugs or drag nonionic fixatives or drugs in an ionic solution.
• Iontophoresis is useful in the present invention because it facilitates both transport of the fixative or drug out of the polymer matrix 12 and tissue penetration.
• two electrodes are used to develop the required potential or current flow.
• one electrode 18 (the "catheter electrode") is located inside of the polymer matrix 12 while the other electrode is preferably located at a remote site on a patient's skin.
• the other electrode may also, in certain applications, be positioned at other regions of the patient, including appropriate internal areas and may, in fact, also be located along the catheter body at a site removed from catheter electrode 18.
• fixative or other drug within the polymer matrix 12 should have specific characteristics. Ideally, the fixative or other drug should have an ionic nature or have other ionic molecules bound to the fixative or the active components of the drug to promote the iontophoretic movement or transport from the polymer matrix 12.
• An electrical current for the iontophoretic process of Figure 2 is produced between the electrodes 18 and 20 by an external power source 30 through the electrical leads 22 and 24, respectively.
• a fixative or fixation agent is a compound or composition known in the art as a fixative.
• a fixative functions, among other things, to kill, penetrate and harden fresh tissues, to set the tissues so that they will not be altered by subsequent biological or other processing and to render the cell constituents insoluble. Fixatives are commonly used for stabilizing and fixing tissue at the moment such tissue is exposed to the fixative so that histologic slides of the tissue can be prepared or the tissue can otherwise be preserved for examination.
• fixative or fixation solution should rapidly penetrate the plaque and vascular tissue of the vessel in the area of the stenotic lesion. It should quickly kill or otherwise preserve the tissue, while hardening the vascular structure. Such fixation maintains the vessel in an "opened” or dilated condition and prevents or substantially reduces reclosure due to vasospasm or other abrupt reclosure mechanisms. Such fixation also retards or stops the biological processes which lead to gradual restenosis.
• the preferred fixative should also have rapid, specific action in high concentrations, and generally nontoxic actions in lower concentrations.
• the electrode 18 is removed from the polymer matrix 12 and is preferably pulled into holding chamber 19 using wire 16 as shown in Figure 3. Removing electrode 18 from polymer matrix 12 allows the matrix to assume its narrower profile which aids in removal of the catheter from the vessel. It will be understood by those skilled in the art that electrode 18 could also be stored in its original holding chamber 14 if a means of pushing electrode 18 into that chamber after use is provided. In the preferred embodiment however, the wire 16 used to supply power to the electrode 18 cannot supply a compressive force sufficient to push electrode 18 out of the polymer matrix 12. As a result, holding chamber 19 is used to store the electrode after wire 16 is used to pull electrode 18 into holding chamber 19.
• Figures 4-6 depict an alternative embodiment of a catheter constructed according to the present invention.
• the primary difference between this catheter and the catheter of Figures 1-3 is the use of a spring loaded wire basket 56 which, prior to use, is stored in a holding chamber 48 constructed in catheter body 46.
• Construction of the polymer matrix 42 is substantially similar to that described with respect to the embodiment of Figures 1-3.
• the polymer matrix 42 is provided in catheter body 46 in a substantially cylindrical shape. As with the preferred embodiments described above, optional impermeable end caps 43 are provided at either end of the polymer matrix to prevent transport of the drug contained in the polymer matrix 42 axially along the catheter body 46.
• the polymer matrix 42 is also provided with an interior cavity 50 for receiving the spring loaded basket 56.
• Opposite holding chamber 48 in catheter body 46 is holding chamber 52 which is used to store the spring loaded basket 56 after expansion of the polymer matrix 42. Storage of the compressed wire basket 56 in holding chamber 52 is depicted in Figure 6.
• spring loaded basket 56 also serves as an electrode for iontophoretic drug transport in addition to being used to expand the polymer matrix 42.
• Wire 54 provides electric current to the basket 56 during the iontophoresis process as well as moving the basket 56 between holding chamber 48, cavity 50 in polymer matrix 42 and holding chamber 52.
• spring loaded basket 56 is drawn into chamber 50 in the polymer matrix 42 where it expands the polymer matrix. After expansion, the transport process is begun wherein current is provided to the electrode/spring loaded basket 56 via wire 54 to transport the fixative or other drug from the polymer matrix 42 to the appropriate area. After the transport process is completed, the spring loaded basket is drawn further through the catheter body 46 into holding chamber 52 which allows the polymer matrix 42 to return to its narrower profile by compressing the spring loaded basket 56, thus aiding removal of the catheter from the vessel.
• the basket 56 is pulled into position using a wire 54 which is also used to provide current to the basket 56 during iontophoresis.
• wire 54 cannot apply sufficient force to basket 56 to return it to cavity 48 after use. It will, however, be understood that if an appropriate mechanism to do so is used, chamber 52 would be unnecessary.
• FIGs 7A and 7B depict an alternate embodiment of the wire basket design for use in the embodiments depicted in Figures 4-6.
• the basket 70 differs from the basket 56 of the embodiment depicted in Figures 4-6 in that it is manually-loaded as opposed to being spring-loaded. If a manually loaded basket 70 is used, it will be understood that holding chambers 48 and 52 depicted in Figures 4-6 would not be required as the basket would be manually expanded or relaxed as desired by the user.
• FIG 7A depicts the manually-loaded basket 70 in its relaxed or unexpanded state while Figure 7B depicts the basket 70 in its expanded position.
• the basket is expanded by the use of force along wire 72 which extends through the basket to its distal end 74.
• the connection of the basket at point 76 along wire 72 is essentially a slip fit which allows point 76 to move along wire 72 when a force is applied to wire 72.
• the distance between points 74 and 76 is shortened, which translates into expansion of the diameter of the basket 70.
• the manually loaded basket 70 also serves as the electrode when iontophoresis is used to supply the transport mechanism to transport drugs or fixatives from the polymer matrix to the appropriate area.
• One advantage of the manually-loaded basket 70 is the ability of the user to control the amount of expansion of the basket 70 by pulling a specific length of wire 72 from the catheter.
• the wire 72 is supplied with appropriate markings along its length to indicate expansion of the basket 70.
• the polymer matrix of the present invention can also be used in conjunction with a balloon to supply force to enlarge a vessel wall and/or provide intimate contact between a drug-impregnated polymer matrix and the vessel wall.
• the embodiment depicted there includes a polymer matrix 82 located along a section of catheter body 80.
• Optional impermeable end caps 83 are located on either end of the substantially cylindrical polymer matrix 82 in the preferred embodiments.
• the center of the polymer matrix 82 contains an inflatable balloon 84 which is surrounded by a substantially cylindrical and expandable electrode 86 which could take the form of an expandable wire mesh.
• the balloon 84 is inflated through lumen 85 using any appropriate fluid or gas.
• electrode 86 expands with balloon 84 and is used to provide current to transport the drugs or fixative contained in the polymer matrix 82 to the surrounding tissue. Electric current is provided to the electrode 86 using wire 87 which runs alongside lumen 85.
• FIGS 9A and 9B depict an alternate embodiment of a catheter 90 incorporating a balloon 92 and polymer matrix material 94.
• the catheter body 96 includes a core 98 extending through the balloon 92, around which the electrode 100 is wrapped in a coil fashion.
• Catheter body 96 also includes central guide wire lumen 105.
• the balloon 92 consists of a substantially cylindrical section of a porous, elastic material which is attached along either end to the catheter body 96 using an adhesive or heat weld.
• the polymer matrix material 94 is disposed on the outer surface of the balloon 92 for intimate contact with a vessel wall 101 after expansion (see Figure 9B) .
• the balloon 92 is expanded with a fluid supplied through fluid-supply lumen 102 while wire lumen 104 houses the wire 106 which supplies current to the electrode.
• the fluid used to expand the balloon 92 is preferably either water or a weak electrolyte solution to enhance current flow through the polymer matrix material 94 which, in turn, enhances drug delivery to the target tissue.
• Figure 10 depicts a catheter substantially similar to the catheter 90 disclosed in Figures 9A and 9B, with the substitution of a transducer 108 for the electrode of catheter 90.
• the transducer 108 is used to produce sonic energy which moves drug from the polymer matrix material 110 using phonophoresis in the place of iontophoresis.
• Power is supplied to the transducer 108 using wire 109 which runs through a wire supply lumen.
• the preferred fluids used for expansion of the balloon 112 include water or saline, although any fluid used to expand the balloon 112 need only provide the physical properties which enhance the propagation of sonic energy from the transducer 108 to the polymer matrix 110 and, finally, to the target tissue for delivery of the drug.
• catheters according to the present invention can also be used to deliver any drug to or through a vessel wall.
• each of the above embodiments of Figures 1-10 may be used for such drug delivery and each embodiment would be useful for delivering an antitumor, antihyperplastic or other agent through a vessel wall to a nearby or adjacent tumor or other internal body tissue.
• a drug may be delivered substantially transversely to the longitudinal axis of a body passageway to treat a localized region of tissue located adjacent to the passageway by using iontophoresis to drive through the passageway wall and into the surrounding or adjacent tissue.
• any of the foregoing alternative embodiments of the apparatus as seen in Figures 1-10 may also be used for such drug delivery.
• tumors may be treated by delivering certain drugs through blood vessels or the intestinal tract or whatever to adjacent tumor sites.
• the present invention is well suited to delivery of sensitizer and immunomodulator drugs.
• sensitizer and immunomodulator drugs for the purposes of primary or adjuvant treatment or other circumstances where drug delivery to a specific local or regional internal body tissue site such as a solid tumor, abscess, regional lymph nodes or the like is desired, further embodiments of the present invention as shown in Figure 11 are preferred.
• the tissue delivery system shown in Figure 11 includes a drug delivery apparatus 120 that is positioned into a specific tissue, such as a tumor.
• the preferred drug delivery apparatus 120 for treating internal body tissue includes a flexible catheter body 121 and substantially cylindrical polymer matrix 124. Positioned in the polymer matrix 124 is an electrode 128 which is connected to wire 130 which extends to the proximal end of the catheter 120. In use, the catheter body 121 is moved into position. The drug is then driven out of the polymer matrix 124 by a voltage gradient (iontophoresis) using electrode 128.
• a voltage gradient iontophoresis
• apparatus 120 can range in size from very large (trocar) to very small (tenths of mm), depending on the type and location of internal body tissue to be treated.
• the embodiment in Figure 11 preferably utilizes iontophoresis to drive the drug from the polymer matrix 124.
• Iontophoresis is preferred because it facilitates both transport of a fixative or drug and enhances tissue penetration.
• the catheter electrode 128 is located within the polymer matrix 124, while the other electrode (not shown) is preferably located on the body of the patient.
• the other electrode may also, in certain applications, be positioned at other regions of the patient, including appropriate internal areas and may, in fact, also be located along the catheter body at a site removed from catheter electrode 128.
• the introducer (not shown) is placed into the target area, which may be a tumor or the like, after identification of the position of the lesion mechanically, radiographically, thermally, ultrasonically, or through some other like methodology.
• the trocar/probe can be designed for steerability to facilitate positioning into the tumor. This can be accomplished by simply placing a bend in the trocar or by other mechanical design techniques known to those skilled in the art.
• the active apparatus 120 is then passed through or over the introducing element directly over the inducer or through the void left in the intervening tissue by the withdrawal of the introducer. After apparatus 120 is in place, as confirmed by one of the foregoing methods, the active compound is delivered from the polymer matrix 124 into the local or regional tissue. Using an embodiment of apparatus 120 of the type seen in Figure 11, the delivery is accomplished iontophoretically.
• the active compounds delivered to an internal body tissue using apparatus 120 include, but are not limited to, antitumor agents such as the vinca alkaloids, anthracycline antibiotics, platinum analogs, antimetabolites (e.g., methotrexate) ; antibiotics; sensitizers or other compounds,
• the advantage of this method is that it allows delivery of the drug into the interstitial fluid and into the cells of the target area themselves even if the vasculature of the area is severely compromised and the cells do not preferentially take up the drug.
• phonophoresis (sometimes referred to as sonophoresis) can be used as an alternative to iontophoresis to transport drugs from the polymer matrix into the surrounding tissue.
• Phonophoresis is the use of ultrasonic or high frequency sound waves to transport drugs.
• phonophoresis has several advantages over iontophoresis, including the ability to achieve greater penetration and to more readily deliver an entire molecule, rather than an ionically charged form of the drug.
• Prior applications of phonophoresis have been limited to transdermal delivery of drugs such as anti-inflammatory agents and local anesthetics through the skin to treat epicondylitis, tendonitis, bursitis and osteoarthritis.
• Phonophoresis is also well-suited for driving fixatives or drugs from the polymer matrix material of the present invention to localized body passageways or internal tissues because it facilitates both transport of a fixative or drug from the polymer matrix and enhances tissue penetration.
• ultrasound may be advantageously used with the catheter of the present invention based on the increased tissue temperature, tissue hyperemia and increased capillaiy permeability associated with ultrasound. These actions can enhance intra-tissue drug transport and cellular uptake as well as cause vasodilation/relaxation which may be beneficial in vascular drug applications using catheter embodiments of the type described herein.
• the cathode electrode is replaced by an ultrasonic piezoelectric transducer (barium titanate, lead zirconate titanate, or the like), which is connected to the external power source. After the catheter is in place, the ultrasonic transducer is activated to transport drugs or fixatives into tissue surrounding the catheter.
• an ultrasonic piezoelectric transducer barium titanate, lead zirconate titanate, or the like
• the diffusion rate of drugs delivered by phonophoresis depends upon the intensity and frequency of the ultrasonic field.
• Prior transdermal applications of phonophoresis use intensities of 0.1 to 6 watts/cm 2 and involve direct correlation between the amount of drug diffused and the intensity of the ultrasonic field.
• Internal applications (not requiring transdermal delivery) of phonophoresis with the catheter embodiments of the present invention are envisioned to require significantly less intensity to deliver an equal amount of drug.
• Various frequencies can be used. A frequency of about 1 MHz has been optimally used in transdermal phonophoresis. It is envisioned that approximately 1 MHz or less can be used for internal applications of the catheter embodiments described herein.
• an additional feature that can be incorporated in catheters according to the present invention is a protective covering over the polymer matrix material.
• a protective covering may be useful with some polymer matrix materials which are not as dimensionally stable as others and could be particularly sensitive to shearing and/or abrasion during insertion and removal. The shearing and/or abrasion may cause portions of the polymer matrix material to remain in the patient after treatment.
• catheters according to the present invention can be fitted with protective coverings that take a number of forms.
• a protective covering is depicted in Figures 12A and 12B, where the catheter 132 includes an outer sheath 134 which covers the polymer matrix 136 during insertion of the catheter 132.
• the sheath 134 is retracted to expose the polymer matrix 136 and drug delivery can proceed (either with expansion of the polymer matrix as depicted in Figure 12B or with delivery of the drug without expansion) .
• the sheath 134 is then extended to again protect the polymer matrix 136 during removal of the catheter 132.
• the sheath 134 in this embodiment of the protective covering is preferably constructed of a rigid material to provide consistent retraction and extension characteristics.
• An additional advantage of the sheath 134 is that the material used for its construction is also typically impermeable to the drug contained in the polymer matrix 136. That impermeability prevents delivery of the drug in the polymer matrix through passive diffusion to tissue encountered during insertion or removal of the catheter 132, thus enhancing the dosage accuracy of the catheter 132.
• FIG. 13 An alternate protective covering is depicted in Figure 13, where an outer membrane 144 covers a polymer matrix (not shown) in catheter 140. It will be understood that catheter 140 could take the form of any of the catheters described in detail above.
• the membrane 144 is porous to the drug contained in the polymer matrix to allow transfer through the membrane 144 using either iontophoresis or phonophoresis.
• outer membrane 144 is constructed of a flexible material it can be used in catheters in which the polymer matrix material 142 is expanded with an electrode, transducer, wire basket or inner balloon (all of which are described in detail above) . If expandable, the membrane 144 can be loosely fit around the polymer matrix to allow room for expansion. In the alternative, if the membrane 144 is elastic or stretchable, its fit around the polymer matrix can be tighter as the membrane can then stretch around the expanded polymer matrix.
• the porous membrane 144 also protects the polymer matrix from shearing and abrasion and also offers some degree of protection from passive diffusion during insertion and removal of the catheter 140 (although the membrane 144 is porous by its very nature) .
• portions of the membrane 144 can be impermeable (non-porous) to further control delivery of the drug in the polymer matrix.
• the impermeable portions would preferably located on either end of the membrane 144 to limit or prevent drug delivery in an axial direction along the body of the catheter 140.
• This design is particularly useful in expanding catheters, as after expansion of the polymer matrix and associated membrane 144, the porous portions of the membrane 144 would be in intimate contact with the vessel wall or target tissue, while the remaining sections of membrane 144 which are not in intimate contact would be impermeable, thereby limiting unwanted drug transfer in the axial direction.

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• 1992
  • 1992-12-15 JP JP6507155A patent/JPH07500523A/ja active Pending
  • 1992-12-15 WO PCT/US1992/010839 patent/WO1994005361A1/en not_active Application Discontinuation
  • 1992-12-15 AU AU33212/93A patent/AU3321293A/en not_active Abandoned
  • 1992-12-15 EP EP93901354A patent/EP0611311A1/de not_active Withdrawn

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