Inflatable medical devices   

CROSS-REFERENCE TO RELATED APPLICATIONS

This application claims priority to U.S. Provisional Application Nos. 61/057,986, filed Jun. 2, 2008; 61/086,739, filed Aug. 6, 2008; 61/105,385, filed Oct. 14, 2008; and 61/205,866, filed Jan. 22, 2009 which are incorporated by reference herein in their entireties.

BACKGROUND OF THE INVENTION

1. Field of the Invention

This invention relates to inflatable structures for use in medicine and other applications, and methods of manufacture and use of the same.

2. Description of the Related Art

Inflatable structures, such as balloons, are widely used in medical procedures. A balloon is inserted, typically on the end of a catheter, until the balloon reaches the area of interest. Adding pressure to the balloon causes the balloon to inflate. In one variation of use, the balloon creates a space inside the body when the balloon inflates.

Balloons may be used to move plaque away from the center of a vascular lumen toward the vasculature walls, such as during an angioplasty or a peripheral vasculature procedure. During this procedure, a balloon tipped catheter is placed in a vascular obstruction. As the balloon is inflated, the vessel constriction is dilated, resulting in improved blood flow.

Optionally, the balloon may have a stent placed over it. The balloon expands the stent in order to create a scaffold structure that keeps the vessel from constricting after the balloon is removed. Stents are used throughout the body, including the coronaries, other portions of the vasculature, the GI tract, the biliary ducts and the urinary and gynecologic tracts.

High pressure balloons may be used to expand constrictions in bone, such as in the sinuses in sinuplasty.

Balloons may be designed to make space in bone. After an osteoporotic compression or trauma-induced fracture in a vertebral body, a balloon can be inserted into the vertebral body through a working channel such as a cannula. The balloon is then inflated, creating a void in the bone. The balloon is withdrawn and bone cement is injected to internally stabilize the fracture. This procedure may be referred to as Kyphoplasty.

Sometimes the vasculature has a narrowing that is calcified, which can create a particularly difficult obstruction for dilation. As the vessel is increasingly narrowed, it can become what is known as a CTO (Chronic Total Occlusion). CTOs can be difficult to pass through with a device such as a guidewire or catheter and can be difficult to dilate or open. The balloon used to open a CTO is ideally resistant to puncture and operates at a very high pressure.

Balloons can have structures attached to their surface. These structures can include blades or stiffening rods. These structures may slice a vessel open. These structures may apply pressure to the inside of a vessel in order to expand the vessel.

Balloons can be used to locally deliver captured volumes of a radioactive substance. The procedure may be known as brachytherapy.

Balloons can be used to intentionally obstruct vessels. Stenting of the carotids serves to treat atherosclerotic carotid vessels. Stenting of the carotids may be less invasive than an endarterectomy. Stenting of the carotids may release a stream of debris that can travel to the brain, causing strokes. Expanding a balloon in the carotid artery above the area of treatment can prevent this debris movement to the brain, thereby reducing the potential for adverse complications.

Balloons may be used to position and deploy arterial grafts that repair aneurysms.

A balloon may deliver targeted drugs in the body by isolating a space for treatment.

A balloon may deliver targeted drugs in the body by having many tiny holes in the balloon wall. The holes in the balloon wall may allow the drug to slowly flow into the area surrounding the balloon.

Balloons may be used endoscopically to open up constrictions in the body, such as those in the esophageal tract, the urological tract, the biliary tract, the fallopian tubes, the carpal tunnel or esophagus, or other portions of the GI tract (the alimentary canal). A balloon may be used to expand constrictions in the urethra, including for Benign Prostate Hyperplasia (BPH).

Balloons may be used in the heart valves, including during Percutaneous Transvenous Mitral Valvuloplasty (PTMV) or Percutaneous Transvenous Mitral Balloon Commissurotomy (PTMC) or Mitral Annuloplasty. The balloons can be utilized to expand stenosed or calcifically-narrowed structures. The balloons can be utilized to expand valves to a tissue-opposed diameter.

A balloon may be used to affix a device inside the body. Another device may then use the balloon as a structure that the device can react against. The device may use this reaction force to move in the body. A balloon and a device may be used in the GI tract. A balloon and a device may be used during a Double Balloon Enteroscopy procedure, or during colonoscopy.

Balloons may be used to create space in the body or to move organs in body. Balloons can be used to manipulate organs along tissue planes.

The balloon may locate a cutting instrument in some ablative procedures. The balloon may position a diagnostic device.

An inflatable structure can be used to open space in tissue or to pull sclerotic structures apart, or to advance structures introduced herewithin to the body.

A balloon may be used to occupy a volumetric space for long periods of time, such as a device used to impart satiety at lower food volumes, as in Bariatric procedures.

A balloon can be used to create captured volumes that serve to transfer heat or cold. A balloon can provide small crossing profiles that then expand locally to create large volumes with high surface areas and intimate tissue contact. This is utilized in the prostate to treat BPH.

Balloons can be used as implants, creating an anatomical conforming structure advantageous to improved local fit.

Balloons have been suggested which seal against a lumen wall, then continue to dynamically seal as they are manipulated backwards or forwards. These balloons may be used in the GI tract. These balloons may be advanced forward or backward by pressure gradients on either side of the balloon.

Balloons may be used as pressure cuffs, such as those found in Lap-Band bariatric devices. By changing the pressure in the balloon, the inner diameter can grow or shrink. Changing the diameter alters clinical results.

Balloons may be elongated and used for movement through long lumens, including the GI tract.

Inflatable structures can be made into everting tubes, which have been utilized in gynecologic and urinary procedures, and have been suggested for GI procedures.

Two basic types of balloons are utilized: One is a high pressure, low-compliance balloon. The other is a lower pressure, high-compliance balloon.

High-compliance medical balloons are often composed of urethane, latex, silicone, PVC, Pebax, and other elastomers. As the pressure in a high-compliant balloon is increased, the balloon dimensions expand. Once the pressure is reduced, the high-compliance medical balloon may return to its original shape, or near its original shape. High-compliance medical balloons can easily expand several times in volume between zero inflation pressure and burst.

Traditional high-compliance medical balloons can be inadequate for many reasons. High-compliance, or highly elastic medical balloons typically cannot reach high pressures because their walls have a low tensile strength and their walls thin out as the balloon expands. In some instances, high-compliance medical balloons provide insufficient force to complete a procedure. Exceeding the rated pressure of a high-compliance medical balloon creates an excessive risk of balloon failure which can lead to serious complications for the patient.

High-compliance medical balloons also have poor shape control. As a high-compliance medical balloon expands, it may assume a shape dictated mostly by the particulars of the environment inside the patient rather than the clinical goals. In some cases, this can be contrary to what the medical practitioner desires. Many medical procedures are predicated on forming a particular balloon shape reliably.

High-compliance medical balloons often suffer from poor puncture resistance.

It is generally desirable that the medical balloon be able to enter and exit the body with as little trauma as possible. Therefore, a small deflated balloon profile is an important consideration in balloon design. This requirement favors materials with high strength to volume ratios. High-compliance medical balloons do not use materials that have outstanding strength to volume ratios.

In some cases, it is desirable that the medical balloon have a strong chemical resistance. For instance, a principal component of bone cement is methyl methacrylate, which readily degrades some elastomers, such as urethane. Therefore, many high-compliance medical balloons are not compatible with the introduction of aspects of the procedure that the high-compliance medical balloon is meant to support.

Low-compliance, high pressure medical balloons substantially retain their shape under comparatively high pressures. PET (polyethylene terephthalate) is the most common material for use in high pressure low-compliance balloons. PET is commonly used for high-performance angioplasty balloons. PET is stronger than other polymers, can be molded into a variety of shapes and can be made very thin (e.g., 5 μm to 50 μm (0.0002 in. to 0.002 in.)), thus giving these balloons a low profile.

Balloons made from PET walls are fragile and prone to tears. When pressed against a hard or sharp surface in the body, such as bone, PET balloons have poor puncture resistance. PET is very stiff so balloons made from PET may be difficult to pack or fold into a small diameter or with good trackability (i.e., the ability to slide and bend over a guidewire deployed through a tortuous vessel). In some applications, PET\'s chemical resistance can lead to unwanted adhesion, degradation or destruction of a PET balloon during a procedure.

Balloons made from PET, while stronger than most other balloons made from homogenous polymers, may still not be strong enough to hold pressures sufficient to complete certain medical procedures.

The PET in a balloon wall may be oriented during manufacture. However, the oriented PET may not have strength in all directions exactly proportionate to the expected load.

PET, like most low compliance balloons, is usually blow-molded. The blow molding process makes it difficult or impossible to create certain shapes. Blow molding can result in wall thicknesses in the balloon that do not match the material thicknesses to the expected load.

Nylon balloons are an alternative material for low-compliance, high pressure balloons. These balloons are typically weaker than PET balloons and so can contain less pressure. Nylon readily absorbs water, which can have an adverse affect on Nylon\'s material properties in some circumstances. Nylon has improved puncture resistance over PET and is more flexible than PET.

Low compliance fiber reinforced medical balloons have recently become commercially available for peripheral vascular procedures. High strength inelastic fibers are used as part of the low compliance fiber reinforced medical balloons to strengthen the walls of the balloon while further lowering strain rates. High strength inelastic fibers such as Kevlar, Vectran, Dyneema and carbon fiber all have strength to volume ratios that greatly exceed that of PET or Nylon. The high strength inelastic fibers are combined with a flexible adhesive and, optionally, one or more polymer walls to form a balloon.

Low compliance fiber reinforced medical balloons may suffer from several problems. These balloons may have a low volume ratio of high strength inelastic fiber to the total material volume in the balloon walls. It is reasonable to assume that a higher volume ratio of high strength inelastic fiber to the total material volume in the balloon walls would lead to a higher burst pressure for the same wall thickness.

Commercially available low compliance fiber reinforced medical balloons and the processes that produce them may only allow limited flexibility in the placement of the high strength inelastic fibers. For example, a process may result in fibers aligned along the axis of the balloon and fibers wrapped around the circumference. This limited choice of fiber orientation is not always the optimum way to orient the fibers for maximum strength. This limited choice of fiber orientation is not always the optimum way to orient fibers to resist puncture or ripping.

Commercially available low compliance fiber reinforced medical balloons and the processes that produce them may not allow for a large variety of different balloon shapes to be manufactured.

SUMMARY

Medical inflatable devices for use in a biological body are disclosed. The device 2 can have a balloon. The balloon can have a wall having an inner layer, a first middle layer, and an outer layer. The outer layer can be thinner than about 0.05 mm (0.002 in.), and the inner layer is thinner than about 0.05 mm (0.002 in.). The first middle layer can have a fiber. The outer layer can have a melt or decomposition temperature greater than about 200° Celsius.

The outer layer can be made from a thermoset material. The outer layer can be made from PEEK. The outer layer can be made from a polyamide. The outer layer can be MMA-resistant and/or MMA-releasing. An MMA-resistant layer can be substantially non-degrading when exposed to MMA, such as uncured MMA. An MMA-releasing layer can be substantially non-binding or non-adhering to MMA. The MMA-releasing layer can be pulled away and separated from cured MMA without binding to the MMA.

The first middle layer can be made from a resin. The inner layer can be thinner than about 0.01 mm (0.0004 in.), and the outer layer can be thinner than about 0.01 mm (0.0004 in.). The inner layer can be substantially air leak-proof.

The balloon can have a wall that can have an inner layer, a first middle layer, and an outer layer.

The outer layer can be thinner than about 0.05 mm (0.002 in.). The outer layer can have a thermoset material, such as PEEK. The outer layer can have a polyamide. The first middle layer can have a fiber and/or a resin.

The wall can have an air leak-proof inner layer and an MMA-resistant outer layer. The outer layer can be thinner than about 0.05 mm (0.002 in.), and the inner layer can be thinner than about 0.05 mm (0.002 in.).

The second layer can be radially inside the third layer, and the second layer can be radially outside the first layer. The third layer can make up the radial outermost surface of the wall. The wall can also have a fourth layer. The fourth layer can be radially inside the third layer. The fourth layer can be radially outside the first layer. The fourth layer can have a radiopaque material.

The wall can have a first layer, a second layer, a third layer, and a fourth layer. The first layer can be leak-proof and the fourth layer is MMA-resistant. The first layer can be radially inside of the second layer, the third layer, and the fourth layer. The fourth layer can be radially outside of the first layer, the second layer, and the third layer. One, two, or three layers can have resin and fiber in contact with the resin, for example the fiber can be embedded within the resin or in one side of the resin. The layers with the fiber can be MMA-resistant.

The wall can have a layer that can form at least one continuous seam around the balloon. The balloon can be substantially non-compliant or inelastic. The wall can be less than about 0.1 mm (0.004 in.) thick.

The balloon can have a longitudinal axis having a longitudinal axis length. The balloon can have a fiber having a fiber length. The fiber length can be about 175% to about 300% of the longitudinal axis length. The wall of the balloon can have a first layer and a second layer. The fiber can be in the second layer. The first layer can be on the radial inside of the fiber with respect to the balloon, and the first layer can be leak-proof, and/or MMA-resistant.

The balloon can have an inner diameter of more than about 2 mm, or about 13 mm (0.5 in.), or more than about 15 mm. The balloon can have a wall having a wall thickness of less than about 0.005 in., and a burst pressure greater than about 150 psi, more narrowly greater than about 3,400 kPa (500 psi). For example, the burst pressure of the balloon can be greater than about 2,100 kPa (300 psi).

The balloon can have a proximal terminal end and a distal terminal end. The balloon can have a closed distal terminal end, or no through-lumen. Having no through-lumen can include having no longitudinal through-lumen extending through the proximal terminal end and through the distal terminal end. The distal end of the balloon can be atraumatic, for example blunt.

The balloon can have a reinforcement fiber that can be in a matrix. The matrix can have a reinforcement fiber and a resin. The resin can be an adhesive. The fibers can be oriented longitudinally and/or around the distal end of the balloon. The fibers can cover (but not necessarily on the outer surface) greater than 50% of the area of the balloon wall. The matrix can have a thermoplastic material.

The balloon wall can have a first, second and/or more strips. The strips can have none, one or more reinforcement and/or radiopaque marker fibers. Each strip can have the same or a different number of fibers. The balloon can have a closed distal end. The first strip can overlay the second strip at the distal end. Additional strips can overlay the first and second strips at the distal end or elsewhere along the length of the balloon. The strips can intersect at a strip angle. The strip angle can be equal to or greater than about 30 or 45 degrees. For example, the strip angle can be about 60 degrees or about 90 degrees.

The first middle layer can have a radiopaque material and be substantially contiguous throughout the wall. For example, the first middle layer can have a metal foil. The first middle layer can have a radiopaque material in non-powder form. The first middle layer can have less than about 100 pieces of radiopaque material. The radiopaque material can covers (not necessarily on the top surface) at least about 30% of the area of the wall of the balloon. The first middle layer can have a first elongated member that can have a radiopaque material. For example, the elongate member can be a strip, such as the strip described herein.

The first middle layer can have a fiber. The second middle layer can have a radiopaque material. The first middle layer can be between the inner layer and the second middle layer.

The balloon wall can have a water-proof inner layer, a first middle layer that can have a fiber, a second middle layer that can have a radiopaque wire, and an outer layer. The fiber can be helically positioned or hoop or helically wrapped around the balloon wall.

The radially outer layer of the balloon wall can have a thickness of less than about 0.0005 in. and the radially outer layer can be resistant to degradation by MMA. The radially outer layer can be made from or coated with Teflon or PTFE. The MMA-resistant layer can have an MMA-resistant matrix and a fiber. The MMA-resistant matrix can have an adhesive. The balloon can be configured to deliver a radial pressure of about 2,800 kPa (400 psi).

The balloon can be shaped having a first side and a second side. The first side can be opposite the second side with respect to the balloon longitudinal axis. The first side can be substantially flat, and the second side can be substantially flat.

The balloon wall can have a wall thickness of equal to or less than about 0.3 mm, for example about 0.1 mm, and the balloon has an outer diameter less than or equal to about 13 mm, and the balloon has a burst pressure of equal to or greater than about 1000 kPa (150 psi).

The balloon wall can have a first layer that can have a reinforcement and/or marker fiber and a second layer that can have a resistive heating element, such as tantalum foil. The resistive heating element can be a wire helically configured around the balloon. The resistive heating element can be controlled by a controller configured to controllably deliver energy to the resistive heating element. The resistive heating material can be the elongated strip or in the elongated strip.

The wall can have a semi-rigid panel. The panel can be between an inner and outer layer of the wall. The panel can have a modulus of elasticity greater than about 1,000,000 and a thickness greater than about 0.0002 in. The panel can be a metal foil. The balloon can be pleated before use.

A method for making an inflatable device for use in a biological body is disclosed. The method can include forming a leak-proof member from solid film on a removable mandrel. The forming can occur at a temperature below 100° Celsius. the forming occurs without solvation of the film. The method can further include adhering the film to the mandrel, wherein adhering comprises adhering with a water-soluble tacking adhesive. The mandrel can be removed by dissolving the mandrel with water. Forming can include pressure-forming. (i.e., hydroforming with a fluid, even air).

The method can also include trimming the film. The thermoset film can have one or more fibers or no fiber. The film can be substantially anisotropically mechanically load-bearing. For example, the load-bearing properties of the film can be substantially unidirectional along the surface plane of the film.

A method for making the device is disclosed that can include adhering with a first bonding agent a first film to a mandrel, forming the first film on about the first half of the mandrel, bonding with a second bonding agent the first film to a second film, forming the second film on about the second half of the mandrel, and dissolving the mandrel. Dissolving can include applying water to the mandrel. The first bonding agent can be water-soluble. The mandrel can be made from a sugar, a plastic, polylactic acid (PLA), polyvinylacetate, a water-soluble wax, or combinations thereof.

A method for making the device is disclosed that can include positioning a solid film on a mandrel and dissolving the mandrel with the solid film on the mandrel. Dissolving can include dissolving with water. The film can be water-tight. The film can be configured as a flat piece of film before forming on the mandrel. The film can have a square or rectangular shape before forming on the mandrel.

Also disclosed is a method for making the device that can include creating a first hole that transects a mandrel, passing a fiber through the first hole, forming a layer of material on the mandrel, attaching the layer to the fiber, and dissolving the mandrel. Attaching can include attaching the fiber to the side of the layer against the mandrel, attaching the fiber to the side of the layer away from the mandrel, attaching the fiber to the inside of the layer, or combinations thereof.

A method for making the device is disclosed that can include applying fibers to a mandrel, applying an elastomeric resin to the fibers and bonding the fibers to the mandrel. Applying the fibers can include rotating the mandrel while feeding the length of the fibers from a location off the mandrel. The fibers or layer containing the fibers can be bonded to the mandrel or to an adjacent layer to prevent the fibers from slipping against the mandrel or adjacent layer. The mandrel can have an ovaloid shape.

A method for making the device is disclosed that can include applying a first layer of a material on a water-soluble mandrel and forming a thermoset film on the first layer. The method can be performed at a temperature from about 5 degrees Celsius to about 35 degrees Celsius, more narrowly from about 15° C. to about 30° C., for example at ambient or room temperature (e.g., about 18° C. to about 25.5° C.).

A method for making the device is disclosed that can include applying a first layer of a material on a madrel, bonding with a first bonding agent a first thermoset film to the first layer, forming the first thermoset film on about the first half of the first layer, bonding with a second bonding agent the first thermoset film to a second thermoset film, forming the second thermoset film on about the second half of the first layer, and dissolving the mandrel.

A method for making the device is disclosed that can include applying a first layer of a material on a mandrel, hydroforming an MMA-resistant film on the first layer; and dissolving the mandrel with water.

A method for using the device is disclosed that can include inserting the inflatable device adjacent to a target site, expanding the inflatable device to a pressure greater than about 350 kPa (51 psi), and delivering to the target site thermal energy generated in the wall of the inflatable device. Delivering the energy can include singeing or ablating tissue at the target site.

The balloon can be attached to a deployment tool having a deployment rod. The deployment rod can have a rod distal end. The deployment rod can be positioned at least partially inside the balloon when the balloon is in a deflated state. The deployment rod can be slidably adjustable with respect to the location of the proximal end of the balloon. The deployment rod can be in an extended position when the balloon is in the substantially deflated state. The deployment rod can be in a retracted position when the balloon is in the substantially inflated state. The rod distal end can be out of substantial contact with the balloon distal end when the balloon is in the substantially inflated state.

The rod distal end can be in contact with the balloon distal end when the balloon is in the substantially deflated state.

The deployment tool can have a fluid channel configured to deliver fluid to the balloon. When the deployment rod is in an extended position, the deployment rod can substantially obstruct the fluid channel. When the when the deployment rod is in a retracted position, the deployment rod can leave the fluid channel substantially unobstructed by the deployment rod retracting the deployment rod with respect to the balloon, wherein retracting comprises substantially unobstructing fluid delivery through the fluid channel. Further comprising delivering fluid to the balloon after retracting the deployment rod.

The deployment rod can be positioned at least partially inside the balloon when the balloon is in a deflated state. The deployment rod can be fixed with respect to the location of the proximal end of the balloon. The rod distal end can be substantially separate (i.e., not in substantial or any contact) with the balloon wall when the balloon is in the substantially inflated state. The rod distal end can be atraumatic. The rod distal end can have a curved surface facing the balloon distal end. The deployment rod can be stiffer than the balloon when the balloon is in a contracted state.

A method for using the device is disclosed that can include inserting a working channel through the biological body, delivering a first balloon through the working channel and positioning the first balloon at the target site. After the delivering the first balloon, the method can include delivering a second balloon through the working channel and positioning the second balloon at the target site while the first balloon is at the target site. The method can also include delivering an unsupported (i.e., in free air or about standard atmospheric pressure) pressure of greater than about 1400 kPa (200 psi) to the first and/or second balloon. The working channel can have an inner diameter less than about 5 mm. The working channel can have a distal port. The distal port can be positioned adjacent to, or at, the target site, such as the inside of a vertebral body. The second balloon can be inflated after or concurrent with inflating the first balloon.

The working channel can have an inner diameter less than about 5 mm. The first and second balloons can be attached to separate first and second deployment systems, respectively, enabling independent orientation and/or translation of the first balloon from the second balloon, or the first and second balloons can be attached to a single integral joint deployment system.

An inflatable device system is disclosed that can include a curved guide block, a drill, a trocar, a first balloon, a steering mechanism, and combinations thereof. A method for using the system can include positioning a guide block outside of the biological body and delivering a drill through the guide block. The method can include delivering the device through the guide block and into the biological body.

An inflatable device system is disclosed that can have a balloon, a reservoir, a fluid in the reservoir; and a sealed sterile package. The balloon, the reservoir and the fluid can be in the sealed sterile package.

An inflatable device kit is disclosed that can have a balloon having a fully inflated state having an inflated volume, a fluid channel having a fluid channel volume, a sealed reservoir, and a fluid in the reservoir. The fluid in the reservoir can have a fluid volume. The fluid volume can be within 10% of the sum of the inflated volume and the fluid channel volume.

A deployment tool for use with the inflatable device is disclosed that can have a fluid first channel having an incoming port. The fluid first channel can have a luer connector at the incoming port, a check valve and a swabbable valve. The swabbable valve can be adjacent to the luer connector. The check valve can be downstream from the luer connector.

An assembly for use in percutaneously treating a bone predisposed to fracture or to collapse, or that is fractured or collapsed, is disclosed. The assembly can have a cannula, a balloon, a catheter and a driving rod. The balloon can be insertable through the cannula into bone. The balloon can have a deflated condition which has a size for passage through the cannula for insertion into bone. The balloon can be inflated to a predetermined shape and size sufficient for compressing at least a portion of inner cancellous bone so as to form a cavity therein. The balloon can be restrained in the inflated condition to create said predetermined shape and size by having a wall that is thicker in selected portions than it is in other portions and/or by an internal restraint provided in or on the balloon wall and/or by an external restraint in or on the balloon wall. The outer diameter of the catheter can be smaller than the inner diameter of the cannula. The cannula can be adapted to not drive the deflated balloon through the cannula into the bone. The driving rod can releasably attach to the device. The driving rod can be adapted to drive the balloon through the cannula into the bone.

The catheter can have an elastomer and a fiber. The driving rod can have a shaft and a clasp at the distal end of the shaft.

A method for using the device is disclosed that includes inserting a balloon into the target site, inflating the balloon and injecting a load of bone cement into the target site. The load of bone cement can cure while in contact with the balloon. The balloon does not substantially degrade from contact with the load of bone cement. The balloon can have a fiber made from a substantially different material than the remainder of the balloon. Inserting can include inserting with a detachable driving rod. The method can include creating a void at the target site.

The balloon can be non-compliantly expanded. For example, the wall of the balloon can expand no more than about 2% to about 3% strain between the deflated state to the inflated state.

The device can be used to perform valvulopasty, annuloplasty, kyphoplasty, sinuplasty or angioplasty procedures. The device can be used to minimally invasively deliver and expand a vascular stent, graft or heart valve. The device can be used to expand constrictions in the urethra. The device can be used to dilate CTOs. The device can be used to temporarily or permanently occlude vessels, for example to isolate a space within a vessel to locally deliver drugs or to intentionally cause necrosis. The device can be used to deliver therapeutic and/or diagnostic drugs. The device can be used to deliver energy to warm, singe or ablate adjacent tissue. The device can be used as a radiopaque or echogenic marker. The device can be used during a balloon enteroscopy procedure or during colonoscopy. The device can be used to cut, tear, or otherwise rip tissue. The device can be implanted and inflated to create an anatomical feature, such as a breast implant.

FIG. 1 illustrates a variation of the device.

FIG. 2 illustrates a variation of cross section A-A of FIG. 1.

FIGS. 3A through 3C are cross-sectional views of a length of variations of the device.

FIG. 4A illustrates a variation of the device.

FIGS. 4B and 4C are variations of cross-section C-C of FIG. 4A.

FIG. 5A illustrates a variation of the device.

FIGS. 5B and 5C are variations of cross-section D-D of FIG. 5A.

FIG. 6A illustrates a variation of the device.

FIG. 6B is a variation of cross section E-E of the device of FIG. 6A.

FIG. 6C is a variation of cross section F-F of the device of FIG. 6A.

FIG. 6D is a variation of cross section G-G of the device of FIG. 6A.

FIGS. 7 and 8 illustrate variations of the device.

FIG. 9A illustrates a variation of the device in a deflated state.

FIG. 9B illustrates a variation of the device in an inflated state.

FIGS. 10A through 10D illustrate variations of the device.

FIGS. 11A and 11B illustrate partially see-through variations of the device.

FIGS. 11C through 11F are variations of cross-section H-H of FIG. 11A.

FIGS. 12 through 18 illustrate variations of the device.

FIG. 19A illustrates a variation of the device.

FIG. 19B is a variation of cross section i-i of FIG. 19A.

FIG. 20A illustrates a variation of the device.

FIG. 20B is a variation of cross section JJ of FIG. 19A.

FIGS. 21A and 21B are top and bottom perspective views, respectively, of a variation of the device.

FIG. 22A illustrates a variation of the device.

FIG. 22B is a variation of cross-section K-K of FIG. 22A.

FIG. 23A illustrates a variation of the device.

FIGS. 23B and 23C are variations of cross-section L-L of FIG. 23A.

FIG. 24A illustrates a variation of the device.

FIG. 24B is a variation of cross-section M-M of FIG. 24A.

FIGS. 25 through 28 are cross-sectional views of variations of the device.

FIG. 29A illustrates a variation of the device.

FIG. 29B is a variation of cross-section N-N of FIG. 29A.

FIGS. 30A through 34A illustrate variations of the device.

FIGS. 30B through 34C are variations of cross-sectional views P-P through T-T respectively, of FIGS. 30A through 34A, respectively.

FIG. 35A illustrates a variation of the device.

FIG. 35B is a variation of cross-section U-U of FIG. 35A.

FIG. 36A illustrates a variation of the device.

FIG. 36B is a variation of cross-section V-V of FIG. 36A.

FIG. 37A illustrates a variation of the device.

FIG. 37B is a variation of cross-section W-W of FIG. 37A.

FIG. 38A illustrates a variation of the device.

FIGS. 38B, 38C and 38D are variations of cross-section X-X and Y-Y of FIG. 38A.

FIG. 39A illustrates a variation of the device.

FIGS. 39B, 39C are variations of cross-section Z-Z and AA-AA respectively of FIG. 39A.

FIG. 40 illustrates a variation of the device.

FIGS. 41A and 41B illustrate a variation of the device in deflated and inflated configurations, respectively.

FIGS. 42A-42E are partial see-through views of variations of the device.

FIG. 43 illustrates a variation of an elongated element or strip.

FIG. 44 illustrates a variation of an element of the device.

FIG. 45 illustrates a variation of the device.

FIGS. 46A through 46P are sectional views through variations of cross section BB-BB of FIG. 1.

FIGS. 47 through 49 are tables listing film materials, reinforcement materials, and adhesive and matrix materials, respectively.

FIG. 50 illustrates a variation of a tool for manufacturing a variation of the inflatable device.

FIG. 51 is a variation of cross-sectional view CC-CC of FIG. 50.

FIG. 52 is a chart of material characteristics for variations of mandrel materials.

FIGS. 53 through 58 illustrate a variation of a method for manufacturing the device.

FIGS. 59A through 59H illustrate a method of making fiber tape.

FIGS. 60 through 67 illustrate a variation of a method for manufacturing the device.

FIG. 68 illustrates a variation of a method for removing the mandrel.

FIG. 69 illustrates a variation of the device in an inflated state before being pleated.

FIG. 70 illustrates a method of adding pleats or folds to a variation of the device.

FIG. 71 illustrates a variation of the device in a deflated, pleated state.

FIG. 72 illustrates a portion of a method that may be used to produce unidirectional fiber tape.

FIG. 73 illustrates a portion of a method that may be used to produce unidirectional fiber tape.

FIGS. 74 through 77 illustrate variations of arrangements of unidirectional fiber tape.

FIG. 78 illustrates a variation of a method for making a laminate.

FIG. 79 is a process flow chart of a variation of a process for making a laminate.

FIG. 80 is a graph illustrating a variation of temperature and pressure verse time graph for a method for compacting or curing or melting that can be used with a fiber tape.

FIG. 81A-81D illustrates a variation of the mandrel.

FIG. 82A illustrates a variation of a manufacturing tool.

FIG. 82B is a variation of cross-sectional view GG-GG of FIG. 82A.

FIG. 83 illustrates a variation of the fiber during a variation of a method for manufacturing the device.

FIG. 84 is a variation of cross-sectional view GG-GG of FIG. 82A.

FIG. 85 illustrates a variation of the fiber during a variation of a method for manufacturing the device.

FIG. 86 illustrates a variation of a method for manufacturing the device.

FIG. 87 illustrates a variation of the fiber during a variation of a method for manufacturing the device.

FIG. 88 illustrates a variation of a method for manufacturing the device.

FIGS. 89 through 91D illustrate variations of a method for manufacture of the device.

FIGS. 92 through 94 illustrate variations of methods for manufacturing the device.

FIGS. 95 through 100 illustrate variations of laminate sheets.

FIGS. 101 through 107 illustrate a method for manufacturing the device.

FIG. 108A illustrates a variation of a tool for manufacturing a variation of the inflatable device.

FIG. 108B is a variation of cross-sectional view 11 of FIG. 108A

FIGS. 109 through 115 illustrate a variation of a method for manufacturing the device.

FIGS. 116 through 119 illustrate a method for manufacturing the device.

FIG. 120 illustrates a variation of a layer.

FIGS. 121 and 122 illustrate variations of elongated elements.

FIGS. 123 and 124 illustrate variations of three overlayed elongated elements.

FIGS. 125 though 127 illustrate variations of methods for manufacturing the device.

FIG. 128A illustrates a variation of a manufacturing tool.

FIG. 128B is a variation of cross-sectional view LL-LL of FIG. 128A.

FIG. 128C is a close-up view MM-MM of FIG. 128B.

FIG. 129 is a partial see-through view of a sagittal view of a spine in a patient.

FIG. 130 is a partial see-through coronal view of a vertebra.

FIGS. 131, 134, 135, 137, 138, 139 and 140 are coronal cross-sectional views of a variation of a method of using a variation of the device in a vertebra.

FIG. 132 illustrates a cross-section of a variation of the balloon wall.

FIG. 133 illustrates a cross-section of a variation of the balloon contracted inside of the delivery tube.

FIG. 136 is a graph of compliance of the variation of the balloon compared with a typical compliant balloon.

FIGS. 141A through 141I are coronal cross-sectional views of a variation of a method of using a variation of the device in a vertebra.

FIGS. 142A through 142F are coronal cross-sectional views of a variation of a method of using a variation of the device in a vertebra.

FIGS. 143A through 143i are coronal cross-sectional views of a variation of a method of using a variation of the device in a vertebra.

FIG. 144 illustrates a variation of the delivery guide block.

FIGS. 145 and 146 illustrate a variation of a method for using the delivery guide block.

FIGS. 147 through 149 illustrate variations of a deployment tool with the device.

FIG. 150A through 150C illustrate a variation of a method for using the device and the deployment tool.

FIG. 151A illustrates a variation of the deployment tool.

FIG. 151B illustrates the proximal end of the variation of the deployment tool during use.

FIG. 151C is a variation of cross-sectional view PP-PP of FIG. 151A shown in a closed configuration.

FIG. 151D is a variation of cross-sectional view PP-PP of FIG. 151A shown in an opened configuration.

FIG. 152A illustrates a variation of the deployment tool.

FIG. 152B illustrates the proximal end of the variation of the deployment tool during use.

FIG. 152C is a variation of cross-sectional view QQ-QQ of FIG. 152A shown in a closed configuration.

FIG. 152D is a variation of cross-sectional view QQ-QQ of FIG. 152A shown in an opened configuration.

FIG. 153 is a variation of cross-sectional view A-A of FIG. 1

FIG. 154A illustrates a variation of the device with a component for inserting the device into the body.

FIG. 154B is a variation of cross-sectional view RR-RR of FIG. 154A.

FIG. 155A illustrates a variation of the device with a component for inserting the device into the body.

FIG. 155B is a variation of cross-sectional view SS-SS of FIG. 155B

FIG. 156 illustrates a variation of a system for using the device.

FIG. 157 illustrates a variation of the deployment rod.

FIGS. 158 and 159 illustrate a variation of a method for using the device.

FIG. 160 is a variation of cross-sectional view TT-TT of FIG. 159.

FIG. 161 is a variation of close-up of FIG. 160

FIG. 162 illustrates a variation of a method for using the device.

FIGS. 163A, 164A, 165A and 166A illustrate variations of the device.

FIGS. 163B, 164B, 165B and 166b illustrate variations of the distal ends of deployment or driving rods configured to interface with the devices of FIGS. 163A, 164A, 165A and 166A respectively.

FIGS. 167, 168 and 169 illustrate sectional views of variations of methods for using a deployment or driving rod with the device.

FIG. 170 illustrates a variation of a method for using a deployment or driving rod with the device.

FIG. 171A illustrates a variation of the shaft of the deployment rod.

FIGS. 171B through 171I are variations of cross-section of FIG. 171A.

FIG. 172A illustrates a variation of a method for using a deployment or driving rod with the device.

FIG. 172B is a variation of cross-sectional view UU-UU of FIG. 172A.

FIGS. 173A and 173B are cross sections of variations of methods of deployment.

FIG. 174A is a variation of a tool for inflating the inflatable device.

FIG. 174B is a variation of a sectional view of FIG. 174A.

FIGS. 175 through 177 illustrate variations of a kit including the device.

FIGS. 178 through 179F illustrate a variation of a method for valvuloplasty.

FIGS. 180A through 180C illustrate a variation of a method for angioplasty.

DETAILED DESCRIPTION

FIG. 1 illustrates that a medical inflatable device 2 can have a balloon 20 and a hollow shaft 2000. An inflation system (shown herein) can be attached to the hollow shaft to deliver a fluid pressure through the hollow shaft and to the balloon. The balloon 20 can be resilient (i.e., elastic) or non-compliant (i.e., inelastic). The balloon 20 can have a balloon longitudinal axis 26. The balloon 20 can have a balloon wall 22. The balloon wall 22 can define a cavity having a balloon volume 24.

FIG. 2 illustrates that the balloon 20 can have balloon length 28. The balloon 20 can have a balloon proximal stem 30 having a balloon proximal stem length 32. The proximal stem length 32 can be from about 5 mm (0.2 in.) to about 15 mm (0.6 in.). The balloon can have a balloon proximal taper 34 having a balloon proximal taper length 36. The balloon proximal taper length 36 can be from about 0 mm (0 in.) to about 20 mm (0.8 in.), more narrowly from about 0 mm (0 in.) to about 15 mm (0.6 in.), yet more narrowly from about 5 mm (0.2 in.) to about 10 mm (0.4 in.) The balloon 20 can have a constant-diameter section 38 having a constant-diameter section length 40. The constant-diameter section length 40 can be from about 0 min (0 in.) to about 15 mm (0.6 in.), more narrowly from about 0 mm (0 in.) to about 10 mm (0.4 in.). The balloon 20 can have a balloon distal taper 42 at the terminal distal end 68 or tip of the balloon 20. The distal taper 42 can have a distal taper length 44. The distal taper length 44 can be from about 0 mm (0 in.) to about 14 mm (0.55 in.), more narrowly from about 2 mm to about 9 mm.

The proximal and/or distal tapers 34 and/or 42 can have concave, convex and/or s-curves. For example, the proximal and/or distal tapers 34 and/or 42 can have continuously varying angles with respect to the balloon longitudinal axis 26.

The balloon 20 can have a wall thickness 46. The wall thickness 46 can be less than about 25 μm (0.98 mil). The wall thickness 46 can be from about 25 μm (0.98 mil) to about 250 μm (9.8 mil), more narrowly from about 50 μm (2 mil) to about 150 μm (5.9 mil), for example about 75 μm (3.0 mil) or about 100 μm (4 mil).