WO2022217398A1 - Expandable balloon catheter - Google Patents

Expandable balloon catheter Download PDF

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Publication number
WO2022217398A1
WO2022217398A1 PCT/CN2021/086402 CN2021086402W WO2022217398A1 WO 2022217398 A1 WO2022217398 A1 WO 2022217398A1 CN 2021086402 W CN2021086402 W CN 2021086402W WO 2022217398 A1 WO2022217398 A1 WO 2022217398A1
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WO
WIPO (PCT)
Prior art keywords
balloon
drug
polymer
balloon catheter
cyclodextrin
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/CN2021/086402
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English (en)
French (fr)
Inventor
Songyun Xu
Lin Wan
Jingjing ZHU
Yirong Gong
Chang PENG
Mian Li
Xueying WEI
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Orbusneich Medical Shenzhen Co Ltd
Original Assignee
Orbusneich Medical Shenzhen Co Ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Orbusneich Medical Shenzhen Co Ltd filed Critical Orbusneich Medical Shenzhen Co Ltd
Priority to CN202180097005.9A priority Critical patent/CN117222446A/zh
Priority to JP2023562728A priority patent/JP7703042B2/ja
Priority to PCT/CN2021/086402 priority patent/WO2022217398A1/en
Priority to EP21936295.1A priority patent/EP4323047A4/en
Priority to US18/554,937 priority patent/US20240189553A1/en
Publication of WO2022217398A1 publication Critical patent/WO2022217398A1/en
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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    • 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
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L29/00—Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
    • A61L29/04—Macromolecular materials
    • A61L29/049—Mixtures of macromolecular compounds
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L29/00—Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
    • A61L29/08—Materials for coatings
    • A61L29/085—Macromolecular materials
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L29/00—Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
    • A61L29/14—Materials characterised by their function or physical properties, e.g. lubricating compositions
    • A61L29/16—Biologically active materials, e.g. therapeutic substances
    • 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
    • A61M25/1027—Making of balloon catheters
    • A61M25/1029—Production methods of the balloon members, e.g. blow-moulding, extruding, deposition or by wrapping a plurality of layers of balloon material around a mandril
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/40—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a specific therapeutic activity or mode of action
    • A61L2300/416—Anti-neoplastic or anti-proliferative or anti-restenosis or anti-angiogenic agents, e.g. paclitaxel, sirolimus
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/60—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a special physical form
    • A61L2300/606—Coatings
    • A61L2300/608—Coatings having two or more layers
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/60—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a special physical form
    • A61L2300/62—Encapsulated active agents, e.g. emulsified droplets
    • A61L2300/622—Microcapsules
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L2420/00—Materials or methods for coatings medical devices
    • A61L2420/08—Coatings comprising two or more layers
    • 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
    • A61M25/1027—Making of balloon catheters
    • A61M25/1029—Production methods of the balloon members, e.g. blow-moulding, extruding, deposition or by wrapping a plurality of layers of balloon material around a mandril
    • A61M2025/1031—Surface processing of balloon members, e.g. coating or deposition; Mounting additional parts onto the balloon member's surface
    • 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
    • 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
    • A61M2025/1075—Balloon catheters with special features or adapted for special applications having a balloon composed of several layers, e.g. by coating or embedding

Definitions

  • the present disclosure relates to an expandable “balloon” catheter used for delivery of a pharmaceutically active agent released upon contact with the walls of a body cavity.
  • the present disclosure relates to an expandable catheter balloon with an improved coating and a method of coating the same.
  • the stenosis or reduction/blocking of the luminal diameter of a diseased blood vessel at one or more sites is commonly treated by applying mechanical expansionary forces to the restriction using minimally invasive techniques such as percutaneous transluminal angioplasty (PTA) and other variants.
  • PTA percutaneous transluminal angioplasty
  • a small flexible plastic tube or catheter to provide access to a guidewire or another instrument (such as a “balloon” catheter) to access the site of restricted flow.
  • the distal end of balloon catheter may be inflated for a short period of time to apply an expansionary mechanical force to the walls of the diseased blood vessel before being withdrawn.
  • a stent may be inserted to maintain the lumen of the vessel after withdrawal of the balloon catheter, although the presence of a stent has been implicated in severe complications which range from acute stent thrombosis to restenosis (reduction in luminal diameter of more than 50%) .
  • the application of expansionary mechanical force to the diseased area initiates a biological response from the tissue, which includes triggering proliferation of dormant smooth muscle cells in the walls of the blood vessel. These smooth muscle cells migrate into the innermost endothelial layers of the blood vessel (tunica media) as part of the healing response.
  • the proliferation and migration of the smooth muscle cells is known as neointimal hyperplasia and together with elastic recoil results in decreased lumen space or restenosis of the vessel. Accordingly, restenosis presents a significant challenge to the effectiveness of angioplasty procedures.
  • a balloon catheter comprising: an expandable portion on an elongated body having a coating extending substantially about the external outer surface of at least the expandable portion; wherein the coating comprising:
  • a primer layer (24) on the surface of the expandable portion comprising at least one or more substantially hydrophilic compounds
  • the active therapeutic agent of the top layer is selected from the group comprising sirolimus, everolimus, paclitaxel and taxol and including derivatives, hydrates, esters, salts, polymorphs or analogs thereof.
  • the mass ratio of inclusion compound and hydrophobic polymer is 1: 1-1: 10
  • the total loading of the active therapeutic agent of the coating of the surface of the balloon is 1-3 ⁇ g/mm 2
  • the at least one or more hydrophilic compound (s) of the primer layer is/are selected from the group comprising polyurethane acrylate, polyvinylpyrrolidone, polyvinyl alcohol, polyethylene glycol and polyacrylic acid.
  • the second layer comprises a homogeneous mixture of the hydrophobic polymer, an active therapeutic agent and the inclusion compound.
  • the second layer comprises microspheres having the active therapeutic agent encapsulated therein.
  • the inclusion compound is chitosan, ⁇ -cyclodextrin, hydroxypropyl- ⁇ -cyclodextrin, hydroxypropyl- ⁇ -cyclodextrin, hydroxyethyl cellulose, carboxymethyl cellulose, iopromide and derivatives thereof and dextran.
  • the hydrophobic polymer carrier may be selected from polylactic acid, polylactide hexalactide and polyglycolide lactide and has a molecular weight of 1-100 kDa.
  • a method of coating a balloon catheter comprising the following steps:
  • a first solution comprising at least one more of the group consisting of from ethanol, acetone, isopropanol, propanol, ethyl acetate, dichloromethane, tetrahydrofuran, acetonitrile and one or more hydrophilic compounds selected from the group consisting of polyurethane acrylate, polyvinylpyrrolidone, polyvinyl alcohol, polyethylene glycol and polyacrylic acid,
  • a second solution comprising at least one or more solvents in the group comprising ethanol, water, acetone and isopropanol into which an inclusion compound has been dissolved;
  • a third solution comprising a therapeutic compound, and a polymer solution in a solvent, said solvent selected from the group comprising ethanol, water, acetone, isopropanol, dichloromethane, trichloromethane and tetrahydrofuran.
  • the step of applying of the solutions to the catheter is performed by dipping, spraying or brushing the solutions thereon.
  • microspheres are formed by aggregation of the therapeutic compound, the polymer and the inclusion compound.
  • FIG 1A depicts an exemplary catheter balloon having two layers.
  • FIG. 1B depicts an exemplary balloon in an embodiment of the present disclosure having three layers.
  • FIG 1C depicts the exemplary balloons of Fig 1A or 1B when positioned on a guidewire in an un-expanded state.
  • FIG 2A depict exemplary balloons according to the embodiment depicted in Fig 1A with cyclodextrin directly coated thereon.
  • FIG 2B (i) – (ii) depict the exemplary balloons of Fig 2A after a second layer (drug coating) has been applied on top of the cyclodextrin layer, before folding.
  • the balloons depicted are coated with beta cyclodextrin at concentration of 50mg/ml (left) , and 100mg/ml (right) and then the balloon was further coated with drug/polymer/dextrin solution.
  • FIG 2C (i) - (ii) depict exemplary balloons of the embodiments depicted in Fig 2A after the cyclo-dextrin and drug coated balloon were folded.
  • FIG 3A depicts the balloon prepared according to the schematic arrangement depicted in Fig 1B with the hydrophilic coating treatment of the first layer and cyclo-dextrin coating of second layer on the inflated balloon outer surface.
  • the surface of the cyclo-dextrin coated balloon is uniform and transparent.
  • FIG 3B depicts the balloon of Fig 3A having the third layer coating of drug/polymer/cyclodextrin applied before folding of the coated balloon
  • FIG 3C depicts the drug/polymer/cyclodextrin balloon of Fig 3B was folded in an unopened state.
  • FIG 3D depicts that the drug/polymer/cyclodextrin coated and folded balloon (shown as Fig 3C) was inflated as 8 atm pressure.
  • FIG 4A (i) depicts a drug/polymer/cyclodextrin coated balloon prepared according to the schematic arrangement depicted in Fig 1B with 66.67%of a weight ratio of sirolimus to polymer PLGA (MW 49700) in the inflated state with 2 atm pressure before folding of the coated balloon.
  • FIG 4B (i) depicts the drug/polymer/cyclodextrin coated balloon prepared according to the schematic arrangement depicted in Fig 1B with 50.0%of a weight ratio of sirolimus to polymer PLGA (MW 49700) in the inflated state with 2 atm pressure before folding of the coated balloon.
  • FIG 4C (i) depicts the drug/polymer/cyclodextrin coated balloon prepared according to the schematic arrangement depicted in Fig 1B with 37.5%of a weight ratio of sirolimus to polymer PLGA (MW 49700) in the inflated state with 2 atm pressure before folding of the coated balloon.
  • FIG 4A (ii) depicts the drug/polymer/cyclodextrin coated balloon prepared according to the schematic arrangement depicted in Fig 1B with 66.67%of a weight ratio of sirolimus to polymer PLGA (MW 49700) prior to coated balloon folding after the coated balloon was folded.
  • FIG 4B (ii) depicts the drug/polymer/cyclodextrin coated balloon prepared according to the schematic arrangement depicted in Fig 1B with 50.0%of a weight ratio of sirolimus to polymer PLGA (MW 49700) after the coated balloon was folded and then the balloon was inflated to 8 atm pressure.
  • FIG 4C (ii) depicts the drug/polymer/cyclodextrin coated balloon prepared according to the schematic arrangement depicted in Fig 1B with 37.5%of a weight ratio of sirolimus to polymer PLGA (MW 49700) after the coated balloon was folded and then the balloon was inflated to 8 atm pressure.
  • FIG 5A (i) depicts the drug/polymer/cyclodextrin coated balloon prepared according to the schematic arrangement depicted in Fig 1B with 50.0%of a weight ratio of sirolimus to polymer PLGA (MW 14300) in the inflated state with 2 atm pressure before folding of the coated balloon.
  • FIG 5B (i) depicts the drug/polymer/cyclodextrin coated balloon prepared according to the schematic arrangement depicted in Fig 1B with 44.44%of a weight ratio of sirolimus to polymer PLGA (MW 14300) in the inflated state with 2 atm pressure before folding of the coated balloon.
  • FIG 5C (i) depicts the drug/polymer/cyclodextrin coated balloon prepared according to the schematic arrangement depicted in Fig 1B with 37.5%of a weight ratio of sirolimus to polymer PLGA (MW 14300) in the inflated state with 2 atm pressure before folding of the coated balloon.
  • FIG 5A (ii) depicts the drug/polymer/cyclodextrin coated balloon prepared according to the schematic arrangement depicted in Fig 1B with 50.0%of a weight ratio of sirolimus to polymer PLGA (MW 14300) after the coated balloon was folded and then the balloon was inflated to 8 atm pressure.
  • FIG 5B (ii) depicts the drug/polymer/cyclodextrin coated balloon prepared according to the schematic arrangement depicted in Fig 1B with 44.4%of a weight ratio of sirolimus to polymer PLGA (MW 14300) after the coated balloon was folded and then the balloon was inflated to 8 atm pressure.
  • FIG 5C (ii) depicts the drug/polymer/cyclodextrin coated balloon prepared according to the schematic arrangement depicted in Fig 1B with 37.5%of a weight ratio of sirolimus to polymer PLGA (MW 14300) after the coated balloon was folded and then the balloon was inflated to 8 atm pressure.
  • FIG 6A depicts a drug/polymer/cyclodextrin coated balloon prepared according to the schematic arrangement depicted in Fig 1B with 66.67%of a weight ratio of paclitaxel to polymer PLGA (MW 49700) in the inflated state with 2 atm pressure before folding of the coated balloon.
  • FIG 6B depicts the drug/polymer/cyclodextrin coated balloon prepared according to the schematic arrangement depicted in Fig 1B with 66.67%of a weight ratio of paclitaxel to polymer PLGA (MW 49700) after the coated balloon was folded.
  • FIG 6C depicts the drug/polymer/cyclodextrin coated balloon prepared according to the schematic arrangement depicted in Fig 1B with 66.67%of a weight ratio of paclitaxel to polymer PLGA (MW 49700) after the coated balloon was folded and then the balloon was inflated to 8 atm pressure.
  • FIG 7A (i) displays the drug 6.52%loss of drug/polymer/cyclodextrin coated balloon with hydrophilic coating treatment of balloon surface after folding process of a balloon embodiment prepared according to the schematic arrangement depicted in Fig 1B.
  • FIG 7A (ii) displays the drug 43.96%loss of drug/polymer/cyclodextrin coated balloon without hydrophilic coating treatment of balloon surface after folding process of a balloon embodiment prepared according to the schematic arrangement depicted in Fig 1B.
  • FIG 7B displays the drug loss ratio of drug/polymer/cyclodextrin coated balloon with the 66.67%, 50.0%, 37.5%of a weight ratio of sirolimus to polymer PLGA (MW 49700) before/after folding coated balloon prepared according to the schematic arrangement depicted in Fig 1B.
  • FIG 7B also displays the drug loss ratio of drug/polymer/cyclodextrin coated balloon with the 50.0%, 44.4%, 37.5%of a weight ratio of sirolimus to polymer PLGA (MW 14300) before/after folding coated balloon prepared according to the schematic arrangement depicted in Fig 1B.
  • FIG 8A depicts the drug elution rate of 66.67%, 50.0%, 37.5%of a weight ratio of sirolimus to polymer PLGA (MW 49700) coated balloon prepared according to the schematic arrangement depicted in Fig 1B against time in the PBS buffer solution at 37 centigrade with 120 RPM shaking. As result shown, 66.67%of a weight ratio of sirolimus to polymer PLGA (MW 49700) coated balloon showed the best elution rate.
  • FIG 8B depicts the drug elution rate of 50.0%, 44.4%, 37.5%of a weight ratio of sirolimus to polymer PLGA (MW 14300) coated balloon prepared according to the schematic arrangement depicted in Fig 1B against time in the PBS buffer solution at 37 centigrade with 120 RPM shaking.
  • FIG 9A depicts a particle size distribution of 66.67%of a weight ratio of sirolimus to polymer PLGA (MW 49700) , PLGA (MW 14300) and PLA (MW15500) coated balloon surface prepared according to the schematic arrangement depicted in Fig 1B by SEM analysis.
  • FIG 9B depicts the particle size distribution of the 66.67%of a weight ratio of sirolimus to polymer PLGA (MW 49700) coated balloon prepared according to the schematic arrangement depicted in Fig 1B analyzed by Scanning Electron Micrograph.
  • FIG 10A depicts the visual example of the 66.67%of a weight ratio of sirolimus to polymer PLGA (MW 49700) coated balloon prepared according to the schematic arrangement depicted in Fig 1B with folding process at 20 times magnitude.
  • FIG 10B depicts the visual example of the 66.67%of a weight ratio of sirolimus to polymer PLGA (MW 49700) coated balloon prepared according to the schematic arrangement depicted in Fig 1B with inflating at 8 atm pressure.
  • FIG 10C (i) depicts the 66.67%of a weight ratio of sirolimus to polymer PLGA (MW 49700) coated balloon as illustrated in FIG 9B at 50 times magnification.
  • FIG 10C (ii) depicts the 66.67%of a weight ratio of sirolimus to polymer PLGA (MW 49700) coated balloon as illustrated in FIG 9B at 200 times magnification.
  • FIG 11A depicts an exemplary experimental arrangement of simulating in vivo conditions with guiding catheter and silica vessel to evaluate the transferred drug content from the 66.67%of a weight ratio of sirolimus to polymer PLGA (MW 49700) coated balloon to silica vessel.
  • FIG 11B is an enlarged view of the artificial silica vessel used in the experimental setup depicted in FIG 10A.
  • FIG 11C (i) depicts a simulated blood vessel (silica vessel) with drug/polymer transferred from an exemplary balloon prepared according to the schematic arrangement depicted in Fig 1B at 20 times magnification.
  • FIG 11C (ii) depicts a simulated blood vessel (silica tube) with drug/polymer transferred from an exemplary balloon prepared according to the schematic arrangement depicted in Fig 1B at x 100 magnification.
  • FIG 12A is a series of measurements simulating the conditions of the drug content in a simulated blood vessel determined using the experimental arrangement of FIG 11A and a balloon produced according to the arranged depicted in schematic representation Fig 1B.
  • FIG 12B is a further a series of measurements simulating the conditions of the drug content in a simulated blood vessel determined using the experimental arrangement of FIG 11A and balloons produced according to the arrangement depicted in schematic representation Fig 1B with varying combinations of compounds.
  • the disclosed technology addresses the need in the art for an improve coating for a balloon catheter which balances various requirements
  • a pharmaceutically active agent is interchangeable with the terms “a pharmaceutical agent” or “drug” .
  • Diseases that can be treated with the present balloon include, but are not limited to, both coronary artery and peripheral artery diseases as well as others.
  • Non-limiting examples of the diseases or conditions that can be treated by the present balloon or method include atherosclerosis, coronary artery atherosclerosis disease (CAD) , peripheral artery atherosclerosis disease (PAD) , narrowing of an artery, etc.
  • CAD coronary artery atherosclerosis disease
  • PAD peripheral artery atherosclerosis disease
  • Atherosclerosis is one of the leading causes of death and disability in the world. Atherosclerosis involves the deposition of fatty plaques on the luminal surface of arteries. The deposition of fatty plaques on the luminal surface of the artery causes narrowing of the cross-sectional area of the artery. Ultimately, this deposition blocks blood flow distal to the lesion causing ischemic damage to the tissues supplied by the artery. Coronary arteries supply the heart with blood. Coronary artery atherosclerosis disease (CAD) is among the most common, serious, chronic, life-threatening illness in the United States. According to the Centers for Disease Control, 370,000 people die annually from CAD and 735,000 Americans have a heart attack or myocardial infarction (https: //www. cdc. gov/heartdisease/facts. htm, retrieved, Feb. 5, 2017) . Narrowing of the coronary artery lumen causes destruction of heart muscle resulting first in angina, followed by myocardial infarction and finally death.
  • Narrowing of the arteries can occur in vessels other than the coronary arteries, including carotid, aortoiliac, infrainguinal, distal profunda femoris, distal popliteal, tibial, subclavian and mesenteric arteries.
  • PAD peripheral artery atherosclerosis disease
  • the prevalence of peripheral artery atherosclerosis disease (PAD) depends on the particular anatomic site affected as well as the criteria used for diagnosis of the occlusion, but as many 8.5 million people in the United States are estimated to suffer from PAD (https: //www. cdc. gov/dhdsp/data_statistics/fact sheets/fs_pad. htm, retrieved, Feb. 5, 2017) .
  • doctors have used the test of intermittent claudication to determine whether PAD is present.
  • the present invention also provides for a method of treating any body cavity by releasing a pharmaceutically active agent from an inflatable balloon through an expandable cover into body cavities other than vascular spaces.
  • a pharmaceutically active agent from an inflatable balloon through an expandable cover into body cavities other than vascular spaces.
  • the genitourinary system including, the urethra, bladder, ureters, penis and vagina
  • gastrointestinal system such as the esophagus, stomach, small intestine or colon
  • the respiratory system including, the trachea, bronchi and alveoli
  • Vascular spaces other than coronary arteries may also be treated, including, the aorta, vena cava (inferior and superior) or neurovascular arteries, e.g., carotid arteries, basilar arteries.
  • the coated balloon of the present invention may also be used to create a cavity within a potential space in the body, e.g., muscle, vascular intima or fibrotic tissue.
  • the pharmaceutically active agent is then released into the new body cavity created from the potential space, e.g., within a muscle.
  • Cancers that can be treated with coated balloon of the present invention include, but are not limited to, bladder, lung cancer, ear, nose and throat cancer, leukemia, colon cancer, melanoma, pancreatic cancer, mammary cancer, prostate cancer, breast cancer, hematopoietic cancer, ovarian cancer, basal cell carcinoma, biliary tract cancer; bladder cancer; bone cancer; breast cancer; cervical cancer; choriocarcinoma; colon and rectum cancer; connective tissue cancer; cancer of the digestive system; endometrial cancer; esophageal cancer; eye cancer; cancer of the head and neck; gastric cancer; intra-epithelial neoplasm; kidney cancer; larynx cancer; leukemia including acute myeloid leukemia, acute lymphoid leukemia, chronic myeloid leukemia, chronic lymphoid leukemia; liver cancer; lymphoma including Hodgkin's and Non-Ho
  • Inflammatory diseases include, but are not limited to, rheumatoid arthritis, systemic lupus eythematosis (SLE) , Crohn's diseases or other collagen vascular diseases. Infectious diseases resulting from bacteria, viruses or prions may also be treated with the balloon of the present invention.
  • w/w means the weight of the pharmaceutically active agent released at any time, t, over total weight of pharmaceutically active agent coated on the balloon; %w/w means w/w ⁇ 100.
  • the present invention may be used with any balloon catheter stent delivery system, including balloon catheter stent delivery systems described in U.S. Pat. Nos. 6,168,617, 6,222,097; 6,331,186; 6,478,814; 7,169,162 or 20090254064. Balloon catheters such as those described in U.S. Patent Pub. No. 20040006359 may also be used with the methods of the present invention.
  • the coating can be applied to a balloon either after the balloon has been compacted for insertion or before insertion.
  • the balloon is compacted by, e.g., crimping or folding.
  • the balloon is delivered to the intervention site by a delivery device such as a catheter.
  • Balloons can be delivered, removed, and visualized during delivery and/or removal by methods well known in the art, see, e.g., U.S. Pat. No. 6,610,013 or 7,171,255.
  • the balloons of the present invention can include, compliant (expand, e.g., 16-40%, when pressurized) , semi-compliant (expand, e.g., 7-16%, when pressurized) , and non-compliant balloons (expand, e.g., 2-7%, when pressurized) .
  • compliant expand, e.g., 16-40%, when pressurized
  • semi-compliant expand, e.g., 7-16%, when pressurized
  • non-compliant balloons expand, e.g., 2-7%, when pressurized
  • the various characteristics e.g., maximum distensions, i.e. distension from nominal diameter to burst, vary and are well known in the art
  • Cutting balloons which are also used in angioplasty may be used with the methods and devices of the present invention.
  • the balloon is inflated to a set inflation pressure which is determined by the operator depending on the site and type of balloon.
  • the “rated burst pressure” or “RBP” of the balloon is the maximum guaranteed pressure to which a balloon can be inflated without failing.
  • the balloon may be coated with a lubricant coating before or after application of the pharmaceutically active agent to reduce the coefficient of friction between the pharmaceutically active and the balloon, i.e., sticking.
  • the lubricant coating may be a hydrophilic or hydrophobic coat.
  • examples of lubricants to reduce the coefficient of friction used in medical devices include: silicone; colloidal solution of water and lecithin; polyphenyl ethers as electrical connector lubricants; and the solid lubricants molybdenum disulphide, PTFE or powdered graphite and boron nitride.
  • the friction coefficients may be reduced as low as 0.001 or less.
  • polymers having non-sticky surfaces can be produced by using a surface modifying compound such as fluoro-containing polymers and copolymers, and the like with vinyl terminal or side groups for chemical solvent resistance and non-sticky surfaces.
  • a surface modifying compound such as fluoro-containing polymers and copolymers, and the like with vinyl terminal or side groups for chemical solvent resistance and non-sticky surfaces.
  • Polymers having hydrophilic surfaces can be produced by using a surface modifying compound such as polyvinylpyrrolidone, PVA, PEG, and the like.
  • polymers having a low surface friction can be produced by using a surface modifying compound such as polyvinylpyrrolidone, PVA, PEG, and the like.
  • a medical device 10 comprising an expandable balloon catheter 12.
  • first layer 16, 26 is applied to the external surface 12, 22 of the balloon.
  • the first layer 16, 26 contains an inclusion compound which is selected from the group consisting of chitosan, ⁇ -cyclodextrin, hydroxypropyl- ⁇ -cyclodextrin, hydroxypropyl- ⁇ -cyclodextrin, hydroxyethyl cellulose, carboxymethyl cellulose and dextran.
  • the first layer comprises ⁇ -cyclodextrin, hydroxypropyl- ⁇ -cyclodextrin, or hydroxypropyl- ⁇ -cyclodextrin.
  • the hydrophobic polymer carrier is selected from polylactic acid, polylactide hexalactide and polyglycolide lactide and has a molecular weight of 1-100 kDa, more preferably 50 kDa.
  • the top layer comprising iopromide as an inclusion compound is applied as a mixture of hydrophobic polymer, an active therapeutic agent and iopomide.
  • iopromide is present as the inclusion compound of the second layer. It is expected that the same function as cyclodextrin can be achieved.
  • the active therapeutic agent of this layer is selected from the group comprising sirolimus, everolimus, paclitaxel and taxol and including pharmaceutically acceptable derivatives, hydrates, esters, salts, polymorphs or analogs thereof.
  • the mass ratio of inclusion compound and hydrophobic polymer is 1: 1-10: 1, more preferably 1-3: 1, for example, the ratio can be 3-1.
  • the total loading of the active therapeutic agent of the surface of the balloon is 0.1–20 ⁇ g/mm 2 , preferably 1-3 ⁇ g/mm 2 , more preferably 1-2 ⁇ g/mm 2 , and most preferably 1.7 ⁇ g/mm 2 .
  • the drug loading of 1.7 ⁇ g/mm 2 is able to achieve the best result, whereby the drug-coated balloon was found to result in minimum drug loss during the delivery process, and the drug can be effectively transferred to the simulated blood vessel wall (over 40%) , leaving behind minimal residual drug on the balloon.
  • a hydrophilic primer layer 24 is applied to at least a substantial portion of the external surface of the expandable portion 12.
  • the primer layer 24 is a coating which comprises a hydrophilic material selected from polyurethane acrylate, polyvinylpyrrolidone, polyvinyl alcohol, polyethylene glycol and polyacrylic acid.
  • the first layer 26 is applied by methods known to persons skilled in the art including dipping, spraying or brushing solutions thereon.
  • the first layer contains an inclusion compound which is selected from the group consisting of chitosan, ⁇ -cyclodextrin, hydroxypropyl- ⁇ -cyclodextrin, hydroxypropyl- ⁇ -cyclodextrin, hydroxyethyl cellulose, carboxymethyl cellulose and dextran.
  • the first layer is ⁇ -cyclodextrin, hydroxypropyl- ⁇ -cyclodextrin, hydroxypropyl- ⁇ -cyclodextrin.
  • cyclodextrin assists the formation of particles of drugs/polymers of the top layer on the surface of the balloon.
  • the size of these polymer/drug particles are large enough that they adhere to the surface of the balloon and adhere with the balloon without being washed away by blood as it is maneuvered to the treatment site. Due to compression by blood vessels at the treatment site and upon expansion of balloon, the drug can be effectively transferred to the blood vessel walls.
  • a top or second coating layer 28 may be applied by dipping, spraying or brushing solutions thereon to substantially overlie the second layer.
  • the second layer comprises a mixture of a hydrophobic polymer, an active therapeutic agent and the inclusion compound of the first layer.
  • the hydrophobic polymer carrier is selected from polylactic acid, polylactide hexalactide and polyglycolide lactide and has a molecular weight of 1-100 kDa.
  • the active therapeutic agent of the top layer is selected from the group comprising sirolimus, everolimus, paclitaxel and taxol and including derivatives, hydrates, esters, salts, polymorphs or analogs thereof.
  • the mass ratio of inclusion compound and hydrophobic polymer is 1: 1-10: 1, more preferably 3-1.
  • the total loading of the active therapeutic agent of the surface of the balloon is 0.1–20 ⁇ g/mm 2 , preferably 1-3 ⁇ g/mm 2 , more preferably 1-2 ⁇ g/mm 2 , and most preferably 1.7 ⁇ g/mm 2 .
  • the active therapeutic agents that can be included in the present invention are preferably small molecules that are hydrophobic in nature.
  • one of the preferred therapeutic agents, sirolimus is a hydrophobic small molecule that can inhibit the proliferation of smooth muscle in blood vessels and prevent blood vessels from being narrowed.
  • the selected hydrophobic polymer is a large molecule that enables the slow release of the active therapeutic agent in blood vessels.
  • both the therapeutic agent and the polymer are hydrophobic compounds, allowing them to co-dissolve and form particular compounds.
  • the inclusion compound e.g. cyclodextrin
  • the inclusion compound is hydrophilic in nature and does not normally dissolve along with therapeutic agent and the polymer. The presence of the inclusion compound assists the formation of particles by the polymers and active therapeutic agent in vivo.
  • the three compounds can be dissolved together, only in a special solvent system in vivo (e.g. one that comprises of ethanol, dichloromethane and water) . If the solvent volatilizes and the balance is interrupted, the polymer and therapeutic agent would be separated from the cyclodextrin.
  • the selected inclusion compounds include cyclodextrin, display great solubility in blood or buffer salt solutions at 37°C, and therefore can dissolve quickly when placed inside human body. Accordingly, the mixture of polymer and drug that stay on the surface of the balloon can easily transfer from the balloon to the blood vessel wall upon contact with and especially upon compression from blood vessels, thereby exerting the therapeutic effect of the drug.
  • inclusion compound e.g. hydrophilic cyclodextrin
  • the inclusion compound, the active therapeutic agent and the hydrophobic polymer together form a homogeneous solution.
  • the organic solvent which may be ethanol and/or dichloromethane
  • the hydrophobic polymer and the active pharmaceutical molecule (drug) aggregate together to form spheres of various sizes.
  • the polymer and the drug (which would normally form a “cake-like” , or “bamboo shoot-like” structure) are present as small particles due to the presence of cyclodextrin.
  • the sphere-shaped particles formed following aggregation are shown in Figure 9B, and they are able to rapidly dissolve in water, blood, or buffer salt solutions.
  • Fig 2A The balloons of Fig 2A were coated with Beta cyclodextrin directly (i.e. without hydrophilic coating treatment applied to the surface of the balloon) in an embodiment according to Fig 1A. At this stage these balloons are shown without a drug coating being applied on top of the cyclodextrin layer.
  • the upper balloon 32 is coated with beta cyclodextrin at a concentration of 50 mg/ml while the lower balloon is coated with beta cyclodextrin at a concentration of 100mg/ml. It can be seen from Fig 2A that beta cyclodextrin is not evenly distributed on these balloons, when beta cyclodextrin is directly coated onto the balloon.
  • Figs 2B (ii) the visual appearance of the catheter balloon after coating with first coating layer of beta cyclodextrin and a top or second layer comprising a drug/polymer and beta cyclodextrin is visible at differing concentrations of the initial coating 50mg/ml, 100mg/ml respectively.
  • Exemplary balloons of the embodiments depicted in Fig 1A prepared with PLGA49700-sirolimus and PLGA14300-sirolimus after folding are shown in Fig 2C.
  • the balloons are prepared with first 50 mg/ml beta-cyclodextrin coating and second sirolimus/polymer PLGA/cyclo-dextrin solution (Fig 2C (i) ) and first 100 mg/ml beta-cyclodextrin coating and second sirolimus/polymer PLGA/cyclo-dextrin solution (Fig 2C (ii) ) , after the cyclo-dextrin and drug coated balloon were folded.
  • FIG 3 there is depicted in more detail the various stages of balloon in accordance with the embodiment depicted in Fig 1B.
  • a coating of Sirolimus (at a drug concentration of 1.7 ⁇ g/mm 2 ) was applied to the external surface of the balloon to cover a substantial portion of the balloon.
  • the surface of the balloon coated with drug/polymer/cyclodextrin solution is uniform, flat and translucent.
  • the drug concentration on the balloon was determined by high-performance liquid chromatography. Specifically, the total amount of drug of the balloon was measured by HPLC, and then divided by the total surface area of the balloon to obtain the concentration of the drug on the surface of the balloon.
  • the balloon of Fig 3B was then folded in an unexpanded state in on itself as shown in Fig 3C by a standard automatic folding device such as MSI FFS1075S.
  • the balloon was then expanded as shown in Fig 3D. It can be seen that notwithstanding the folding and subsequent expansion of the balloon that a significant amount of the drug coating is retained on the balloon, notwithstanding some cracks visible on the drug/polymer/cyclodextrin coating surface on the balloon. The drug/polymer/cyclodextrin coating remains uniform in shape and adhere strongly onto the surface of the balloon.
  • FIG 4A (i) -4C (i) pictures of various balloons with concentrations of sirolimus including 66.67%, 50%, 37.5%together with PLGA 49700 when prepared according to embodiment as shown in Fig 1B have been presented in an expanded state.
  • FIG 4A (ii) –FIG 4D (ii) depicts the balloon after it has been folded and re-expanded. It can be seen that substantial portion of the coating has been retained from visual inspection.
  • FIG 5A (i) -5C (i) pictures of various balloons with concentrations of sirolimus including 50%, 44.44%, 37.5%together with PLGA 14300 when prepared according to embodiment as shown in Fig 1B have been presented in an expanded state.
  • FIG 5A (ii) –FIG 5C (ii) depicts the balloon after it has been folded and re-expanded. It can be seen that substantial portion of the coating has been retained from visual inspection.
  • Fig 6A-C show various photos of a drug/polymer/cyclodextrin coated balloon prepared according to the schematic arrangement depicted in Fig 1B with 66.67%of a weight ratio of pacitaxel to polymer PLGA (MW 49700) at different stages: folding (Fig. 6A) ; un-folding (Fig. 6B) and from folding to deflating (Fig. 6C) .
  • FIG 9A A frequency distribution of the size of particles formed of polymers of various molecular weights (PLA15500, PLGA 4300, PLGA49700) and different concentration of drug as found on the balloon is illustrated in Fig 9A upon a Scanning Electron Micrograph (SEM) analysis particle counting instrument. It is found that the particles on the balloon are in accordance with the requirements of CFDA regulations. This analysis is performed in accordance on the balloons depicted in Fig 1B (with the specified concentrations of sirolimus and Polymer) .
  • SEM Scanning Electron Micrograph
  • Acceptance criteria The number of particles in the 100 mL blank control test should meet Nb ⁇ 1.8; the contamination index of 3 samples should satisfy N ⁇ 270.
  • the contamination index of the three samples measured by the WI-00414 method was 41, which was less than the acceptance standard of 270, showing that all three samples have passed.
  • a Scanning Electron Micrograph of a balloon prepared according to the schematic arrangement depicted in Fig 1B is provided in Fig 9B.
  • the particles of the drug/polymer are formed in a suitable size that allows better adherence to the balloon.
  • Balloons are prepared with coatings prepared by a mixture of PLGA49700 polymer and sirolimus, either with or without surface treatment, that is, the coating of a hydrophilic primer layer as described above in Example 2.
  • the drug content on these balloons is 1.7 ⁇ m/mm 2 before folding. The amount of drug loss caused by the folding process is compared.
  • the drug on the balloon is measured at 0.95 ⁇ m/mm 2 following folding of the balloon using a standard automatic folding machine such as MSI FFS1075S.
  • the reduction of drug concentration from 1.7 ⁇ m/mm 2 to 0.95 ⁇ m/mm 2 represents a loss of approximately 43.96%as demonstrated.
  • Fig 7B depicts various concentrations of sirolimus and polymers before and after folding, showing that there is a relatively low loss of drug from the catheter balloons even after folding has taken place regardless of the amount of drug concentration used in prepared the drug eluted balloons.
  • Fig 8A anumber of different concentrations of sirolimus in combination together with PLGA49700 have been prepared in accordance with the arrangement of layers depicted in Fig 1B.
  • the elution rate of the drug with respect to the ratio of the drug sirolimus with respect to the polymer is determined by using a drug elution test performed in PBS solution with shaking instrument at a shaking speed of 120 RPM and 37°C.
  • a number of different combinations of sirolimus in combination together with PLGA 14300 have also been prepared in accordance with the arrangement of layers depicted in Figure 1B.
  • the elution rate of the drug with respect to the ratio of the drug sirolimus with respect to the polymer is determined in accordance with the same drug elution test as described above.
  • the drug coated balloon was immersed in the 50 mM PBS at 37°C.
  • the drug coated balloon elution system was subject to shaking at a speed of 120 RPM.
  • the sample solution was then collected for HPLC analysis at time 1 min, 3 min and 10 min.
  • FIG 10A An exemplary balloon prepared according to the schematic arrangement depicted in Fig 1B after folding is shown in Fig 10A.
  • the balloon has been soaked and subjected to shaking for 2 minutes in PBS buffer solution (x20) at 120 RPM shaking.
  • FIG 10A An exemplary balloon prepared according to the schematic arrangement depicted in Fig 1B in its unfolded state is shown in Fig 10A.
  • the balloon has been soaked in PBS buffer and subjected to shaking for 2 mins at 37 centigrade and further inflated at 8 atm pressure at 20 times magnitude.
  • Fig 10C (i) and Fig 10C (ii) show the balloon as illustrated in FIG 10B in x50 magnification and x200 magnification respectively.
  • Fig 11A and FIG 11B The in vitro experimental arrangement depicted in Fig 11A and FIG 11B is used to simulate the in vivo release of the pharmaceutically active agent into a vascular space by incubating the balloon which is coated with a pharmaceutically active agent (Sirolimus) in accordance with the embodiment depicted in Fig 1B with three layers, whereby dextrin is used as the inclusion compound and PVP-based hydrophilic layer as described above is included.
  • a pharmaceutically active agent Sirolimus
  • a simulated blood vessel prepared from silica is fixed between plates before being filled with PBS or similar with a pH+7.4 (+/-0.2) .
  • a guide wire is threaded through the simulated blood vessel and an exemplary catheter balloon in an aqueous bath including a buffer such as phosphate buffered saline (PBS) is introduced.
  • PBS phosphate buffered saline
  • the concentration of the pharmaceutically active agent in the aqueous environment may be measured using any means, including, but not limited to, high pressure liquid chromatography (HPLC) or specific immunological assays.
  • HPLC high pressure liquid chromatography
  • the amount of the pharmaceutically active agent released through the expandable cover within about 1 hour when incubated at about 20-25°or about 37°C. in an aqueous environment such as PBS, plasma, blood, abody fluid, or other aqueous medium is assayed.
  • time points may be used to assess release of the pharmaceutically active agent when the balloon is in an unexpanded state or an expanded state, including, but not limited to, within about 30 seconds, within about 1 minute, within about 2 minutes, within about 3 minutes, within about 4 minutes, within about 5 minutes, within about 6 minutes, within about 8 minutes, within about 9 minutes, within about 10 minutes, within about 15 minutes, within about 20 minutes, within about 25 minutes, within about 30 minutes, within about 35 minutes, within about 40 minutes, within about 45 minutes, within about 50 minutes, within about 55 minutes, within about 1 hour, within about 2 hours, within about 3 hours, within about 4 hours, within about 5 hours, within about 6 hours, within about 7 hours, within about 8 hours, within about 1-10 minutes, within about 10-100 minutes or within about 50-200 minutes.
  • the drug/polymer is transferred from the drug eluted balloon to the simulated blood vessel.
  • the drug content amounts are depicted graphically in Fig 8C.
  • Figure 12A demonstrates the content of sirolimus in simulated blood vessel after incubation of balloons formed of different concentrations of dextrin and sirolimus.
  • “150X1-6-4-3” refers to 150mg/ml of dextrin
  • the number “6” refers to concentration of 6mg/ml of dextrin in the first layer of drug coating solution
  • the number “4” refers to the concentration of 4mg/ml of dextrin in the second layer of drug coating solution
  • the number “3” refers to the concentration of 3mg/ml of dextrin in the third layer of drug coating solution.
  • the concentration of the drug is 3mg/ml and the concentration of the polymer is 1.5mg/ml.

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PCT/CN2021/086402 2021-04-12 2021-04-12 Expandable balloon catheter Ceased WO2022217398A1 (en)

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CN202180097005.9A CN117222446A (zh) 2021-04-12 2021-04-12 可扩张球囊导管
JP2023562728A JP7703042B2 (ja) 2021-04-12 2021-04-12 膨張可能バルーンカテーテル
PCT/CN2021/086402 WO2022217398A1 (en) 2021-04-12 2021-04-12 Expandable balloon catheter
EP21936295.1A EP4323047A4 (en) 2021-04-12 2021-04-12 EXPANDABLE BALLOON CATHETER
US18/554,937 US20240189553A1 (en) 2021-04-12 2021-04-12 Expandable balloon catheter

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