Patent Application
20230022616
None.
The present disclosure relates generally to the use of medical devices for the treatment of vascular conditions. In particular, the present disclosure provides materials and methods for using laser-induced pressure waves to disrupt vascular blockages and to deliver therapeutic agents to the blockage area.
Arterial disease is a common disease that affects millions of Americans. Coronary artery disease (CAD) most often results from a condition known as atherosclerosis, which generally manifests as the accumulation of a waxy substance on the inside of a subject's coronary arteries. This substance, called plaque, is made of cholesterol, fatty compounds, calcium, and a blood-clotting material called fibrin. Similarly, peripheral artery disease (PAD) often results from the accumulation of plaque on the inside of a subject's peripheral arteries, such as the arteries in a patient's arms, hands, legs and/or feet.
As the plaque builds up in either coronary arteries, peripheral arteries and other arteries, the corresponding artery narrows and/or becomes stenotic, thereby making it more difficult for blood to flow through the arteries. As the size of the stenosis increases and the blockage worsens, blood flow slows and upon the formation of a total vascular occlusion, blood flow through the corresponding artery completely stops, which in turn may cause pain in the extremities and, in severe cases, gangrene, which may ultimately require amputation.
Balloon angioplasty and other transluminal medical treatments are well-known and have been proven efficacious in the treatment of stenotic lesions at the core of CAD and/or PAD, as long as the artery is only partially blocked and not totally blocked. In a typical angioplasty procedure to treat CAD, a catheter is inserted into the groin or arm of a subject and guided forward through the aorta and into the coronary arteries of the heart. The angioplasty catheter includes a balloon, which when placed within the partial occlusion, can be inflated, thereby dilating the obstruction or restriction and increasing the size of the diameter of the artery to provides more typical blood flow therethrough.
Over time, a vascular occlusion, particularly a total occlusion, may calcify and/or becomes fibrous, thereby decreasing the balloon's ability to dilate the vascular occlusion. Certain types of catheters, such as electrically-induced shockwave balloon catheters, may be used to break the calcified tissue. An electrically-induced shockwave balloon catheter may include a liquid filled balloon and a one or more pairs of electrodes within the balloon. Upon creating a discharge across the electrodes, plasma is produced, which results in the formation of one or more vapor bubbles. The vapor bubbles created within the balloon cause the balloon to expand and contract. The expansion and contraction of the balloon creates a hydraulic force that transfers energy to the vascular occlusion and/or to the walls of the vessel in an amount sufficient to disrupt intraluminal calcium as well as calcium within the tissue layer of the vasculature (for example, calcium deposits). In addition to producing vapor bubbles being upon the formation of plasma generated by the electrical reaction in the liquid, shockwaves are also produced. The shockwaves are transferred through the balloon and to the calcified vascular occlusion, and the shockwaves modify the calcified occlusion.
In the event a total stenotic occlusion forms, it may be difficult for the balloon to enter the stenosis. Additionally, if a total occlusion calcifies and/or become fibrous, thereby increasing the hardness of occlusion, it may become even more difficult, if not impossible, to penetrate the occlusion and insert a balloon catheter. For example, the proximal and/or distal ends of the occlusion may become calcified to the point that “caps” or “calcified caps” are created, such that even an electrically-induced shockwave balloon catheter may be unable to penetrate the calcified total occlusion because the balloon must be within and adjacent the occlusion in order to operate. And because the balloon within an electrically-induced shockwave balloon catheter is typically proximal the distal end of the electrically-induced shockwave balloon catheter, it is unable to be inserted into or through the calcified cap of the total occlusion.
It is also known to use a laser catheter surrounded by a sheath to create a laser-induced pressure waves to disrupt the calcified cap or calcified tissue within the blood vessel to increase vessel compliance. Using a laser catheter to create the pressure waves for disrupting calcium, however, has its challenges, particularly when using a laser catheter to create pressure waves in smaller-sized blood vessels, such as the peripheral vasculature below a patient's knee. Again, it is desirable for the laser catheter to emit a sufficient amount of energy, which will translate into creating a predetermined pressure wave that will disrupt the calcium in the blood vessel itself or the various blood vessel layers. But smaller-sized blood vessels require a laser catheter having a reduced diameter for vessel entry, and the smaller-sized laser catheters may have limitations as to the amount of energy that can transfer. That is, the reduced sized laser catheters may have less optical fibers or smaller diameter optical fibers in comparison to larger sized laser catheters, thereby limiting the amount of energy that the reduced sized laser catheters can transfer before causing damage to the optical fibers. That is, if the optical fibers attempt to transfer too much energy, they will be damaged.
One way to compensate for the reduction in energy transferred through and emitted by the laser catheter includes increasing the amount of contrast in the liquid medium within the outers sheath. Transmitting pulses of light energy into the liquid medium produces vapor bubbles. Upon emitting light from an emitter, such as a laser catheter, within a sheath that contains an absorptive liquid medium, vapor bubbles may be produced within the interior of the sheath and/or exterior to the sheath. Assuming that the vapor bubbles are created on the interior of the sheath, it may be desirable to limit some or all of the potential expansion of the relevant portion of the sheath caused by the vapor bubbles. That is, it may be desirable to reduce the size of the vapor bubbles created within the sheath so as to reduce or prevent the sheath from applying a hydraulic force or pressure to the vascular occlusion and/or to the walls of the vessel. Also, assuming that the vapor bubbles are created on exterior of the sheath within the vessel wall, it may be desirable to reduce and/or prevent the formation of such vapor bubbles so as to reduce or prevent the cavitation event and the formation of the vapor bubbles themselves from applying a hydraulic force or pressure to the vascular occlusion and/or to the walls of the vessel. But increasing the amount of contrast may create an undesirably sized vapor bubble, either within or on the outside of the sheath, thereby potentially damaging the blood vessel.
In other words, the size of the vapor bubble created is dependent at least in part on the degree of absorption of the light energy by the liquid medium as well as total energy deposited by the light source. Generally, the greater the absorption of the light energy by the liquid medium, the greater the force generated by the laser-induced pressure waves. Also, the greater the amount of the light energy delivered to the liquid medium, the greater the force generated by the laser-induced pressure waves. But if the liquid medium absorbs too much energy, an undesirably-sized vapor bubble will form and potentially damage the blood vessel.
What is needed is a device and method for penetrating a calcified and/or fibrous vascular occlusion, particularly a calcified cap(s), and disrupting at least a portion of the vascular occlusion as the device penetrates and traverses the total occlusion. What is also needed is a device that is capable of delivering laser-induced pressure waves to the vascular occlusion in order to disrupt the calcified and/or fibrous portions without applying a hydraulic force thereto. These and other needs are addressed by the various aspects, embodiments, and configurations of the present disclosure. For example, the present disclosure discusses a sheath that has multiple layers to increase the reflective index of the pressure waves without increasing the size of the undesirable vapor bubble. The sheath has a composite structure that mimics anisotropic metamaterial to increase the amplitude of the pressure waves that transmit through the sheath.
An example of a method for improving the compliance of a blood vessel within a subject comprises locating a calcified portion in the media of the blood vessel of the subject, positioning a laser catheter within the vasculature of the subject, the catheter comprising a proximal end a distal end, and at least one emitter disposed adjacent the distal end, positioning a sheath over the laser catheter within the vasculature of the subject, wherein the sheath comprises a proximal end and a distal end, wherein the sheath comprises a first layer forming a lumen, a plurality of pairs of attenuating members and intermediate layers radially exterior the first layer, wherein the attenuating members are constructed of a first material having a first thickness and first durometer, and the intermediate layers are constructed of a second material having a second thickness and a second durometer, wherein the first durometer is greater than the second durometer, wherein the first thickness and the second thickness are different, positioning the sheath within the vasculature such that the attenuating member is disposed adjacent a portion of the calcified portion in the media of the blood vessel, positioning the laser catheter within the vasculature such that the at least one emitter is positioned within the attenuating member and adjacent the portion of the calcified portion in the media of the blood vessel, introducing a liquid medium into the sheath and to the at least one emitter, and emitting a plurality of pulses of light energy from the at least one emitter into the liquid medium, wherein the plurality of pulses of light energy react with the liquid medium and generate a plurality of propagating laser-induced pressure waves that disrupt the calcified portion of media, thereby improving the compliance of the blood vessel.
Another example is the method of the previous paragraph further comprising the step of re-positioning the sheath such that the attenuating member is adjacent another calcified portion of the media.
Another example is the method of any of the previous two paragraphs further comprising the step of re-positioning the laser catheter within the sheath such that the one or more emitters is adjacent another calcified portion of the media.
Another example is the method of any of the previous three paragraphs, wherein the laser catheter is re-positioned within the attenuating member.
Another example is the method of any of the previous four paragraphs further comprising the step of re-positioning the laser catheter within sheath.
Another example is the method of any of the previous five paragraphs, wherein the laser catheter is re-positioned within the attenuating member.
Another example is the method of any of the previous six paragraphs further comprising the steps of removing the laser catheter from the vasculature and removing the sheath from the vasculature.
An example of a method for performing an atherectomy within a subject having a vasculature occlusion within the subject's vasculature comprises inserting a guidewire through a vascular occlusion within the vasculature, introducing a laser catheter into the vasculature and over the guidewire, wherein the laser catheter comprises at least one emitter, ablating at least a portion of the vascular occlusion with the laser catheter, introducing a sheath into the vasculature and over the laser catheter, wherein the sheath comprises a proximal end and a distal end, wherein the sheath comprises a first layer forming a lumen, a plurality of pairs of attenuating members and intermediate layers radially exterior the first layer, wherein the attenuating members are constructed of a first material having a first thickness and first durometer, and the intermediate layers are constructed of a second material having a second thickness and a second durometer, wherein the first durometer is greater than the second durometer, wherein the first thickness and the second thickness are substantially equal, positioning the sheath within the vasculature such that the attenuating member is disposed radially adjacent a calcified portion within the vasculature, positioning the laser catheter within the vasculature such that the at least one emitter is positioned within the attenuating member and radially adjacent the calcified portion, introducing a liquid medium into the sheath and to the at least one emitter, and emitting a plurality of pulses of light energy from the at least one emitter into the liquid medium, wherein the plurality of pulses of light energy react with the liquid medium and generate a plurality of propagating laser-induced pressure waves that disrupt the calcified portion.
Another example is the method of the previous paragraph, further comprising extending the laser catheter distally of the sheath and ablating another portion of a second vascular occlusion, positioning the sheath within the vasculature such that the attenuating member is disposed radially adjacent a second calcified portion of the second vascular occlusion, positioning the laser catheter within the vasculature such that the at least one emitter is positioned within the attenuating member and radially adjacent the second calcified portion, introducing a liquid medium into the sheath and to the at least one emitter, and emitting a plurality of pulses of light energy from the at least one emitter into the liquid medium, wherein the plurality of pulses of light energy react with the liquid medium and generate a plurality of propagating laser-induced pressure waves that disrupt the second calcified portion.
An example of a catheter system of the present disclosure comprises a laser catheter comprising a proximal end, a distal end and at least one emitter disposed adjacent the distal end, a sheath configured to be disposed over the laser catheter and configured to receive a liquid medium, the sheath comprising a proximal end and a distal end, wherein the sheath comprises a first layer forming a lumen, a plurality of pairs of attenuating members and intermediate layers radially exterior the first layer, wherein the attenuating members are constructed of a first material having a first thickness and first durometer, and the and the intermediate layers are constructed of a second material having a second thickness and a second durometer, wherein the first durometer is greater than the second durometer.
Another example is the catheter system of a previous paragraph, wherein the first thickness and the second thickness are different.
Another example is the catheter system of a previous paragraph, wherein the first thickness and the second thickness are substantially equal.
Another example is the catheter system of a previous paragraph, wherein a difference between the first durometer and the second durometer is about Shore 10D.
Another example is the catheter system of a previous paragraph, wherein a difference between the first durometer and the second durometer is about Shore 20D.
Another example is the catheter system of a previous paragraph, wherein a difference between the first durometer and the second durometer is about Shore 30D.
As used herein, “at least one,” “one or more,” and “and/or” are open-ended expressions that are both conjunctive and disjunctive in operation. For example, each of the expressions “at least one of A, B and C,” “at least one of A, B, or C,” “one or more of A, B, and C,” “one or more of A, B, or C,” and “A, B, and/or C” means A alone, B alone, C alone, A and B together, A and C together, B and C together, or A, B and C together. When each one of A, B, and C in the above expressions refers to an element, such as X, Y, and Z, or class of elements, such as X1-Xn, Y1-Ym, and Z1-Zo, the phrase is intended to refer to a single element selected from X, Y, and Z, a combination of elements selected from the same class (for example, X1 and X2) as well as a combination of elements selected from two or more classes (for example, Y1 and Z0).
It is to be noted that the term “a” or “an” entity refers to one or more of that entity. As such, the terms “a” (or “an”), “one or more” and “at least one” can be used interchangeably herein. It is also to be noted that the terms “comprising,” “including,” and “having” can be used interchangeably.
The term “about” when used in conjunction with a numeric value shall mean plus and/or minus ten percent (10%) of that numeric value, unless otherwise specifically mentioned herein.
The term “attenuating member” as used herein is any component which alters a cavitation event, and/or vapor bubble. An example of an attenuating member is an element which minimally affects the laser induced pressure wave, yet alters the cavitation event and/or the vapor bubble. An example of an attenuating member is a porous attenuating member. The attenuating member, however, does not need to be porous and may include a solid configuration.
The term “catheter” as used herein generally refers to a tube that can be inserted into a body cavity, duct, lumen, or vessel, such as the vasculature system. In most uses, a catheter is a relatively thin, flexible tube (“soft” catheter), though in some uses, it may be a larger, solid, less flexible—but possibly still flexible—catheter (“hard” catheter). In some uses a catheter may contain a lumen along part or all of its length to allow the introduction of other catheters or guidewires. An example of a catheter is a sheath.
The term “balloon catheter” as used herein generally refers to the various types of catheters which carry a balloon for containing fluids. Balloon catheters may also be of a wide variety of inner structure, such as different lumen design, of which there are at least three basic types: triple lumen, dual lumen and co-axial lumen. All varieties of internal structure and design variation are meant to be included by use of the term “balloon catheter” herein. In some uses, balloon catheters can be used to perform angioplasty.
The term “cavitation event” as used herein describes the rapid fluid movement that leads to collapse of a vapor bubble to its smallest radius. In some cases, a cavitation event may include the generation of a pressure wave.
The terms “coupler” or “fiber optic coupler” refers to the optical fiber device with one or more input fibers or emitters and one or several output fibers or emitters. Fiber couplers are commonly special optical fiber devices with one or more input fibers or emitters for coupling these fibers or emitters to an energy source. The energy source can be another optical energy carrying fiber or emitter which is coupled to one or more additional fibers or emitters.
The term “emitter” as used herein refers to a fiber or an optical component (including any portion thereof, such as the end of a fiber) that emits light from a distal end of device, such as a catheter, towards a desired target. In some uses, this target can be tissue, or an absorptive media, such as contrast fluid. An emitter can be the output end of any device that transports light from an optical energy source to a target or treatment area. These optical energy transport devices can include glass or fused silica fiber optics, plastic fiber optics, air or gas light guides, and liquid light guides. As described herein, an emitter or emitters can be used to emit light of any wavelength. An emitter or emitters can emit light, including but not limited to, laser light, white light, visible light, infrared light, and ultraviolet light.
According to the present disclosure, the catheter contains at least one emitter, which may comprise glass or fused silica fiber optics, plastic fiber optics, air or gas light guides, and liquid light guides. Examples of a liquid light guide, or a catheter that contain a liquid light guide can be seen in U.S. application Ser. No. 11/923,488, filed Oct. 24, 2007 and U.S. application Ser. No. 12/254,254, filed Oct. 20, 2008, both of which are hereby incorporated herein by reference in their entireties for all that they teach and for all purposes.
The term “flexible structure” as used herein shall mean a structure that is able to bend or otherwise conform to the shape of the vasculature as it passes therethrough. The term “radial flexible structure” shall include a flexible structure that is also able to expand and/or contract in the radial direction upon a laser induced pressure wave passing therethrough.
A “laser emitter” as used herein refers to an end portion of a fiber or an optical component that emits laser light from a distal end of the catheter towards a desired target. In some uses, this target can be tissue, or an absorptive media, such as contrast fluid.
The term “laser-induced pressure wave” as used herein is a pressure wave caused by a reaction between laser light and an absorptive material. The laser-induced pressure wave may be generated in a gas, liquid (e.g., saline that may or may not include a contrast medium) or solid.
The term “means” as used herein shall be given its broadest possible interpretation in accordance with 35 U.S.C. § 112(f). Accordingly, a claim incorporating the term “means” shall cover all structures, materials, or acts set forth herein, and all of the equivalents thereof. Further, the structures, materials or acts and the equivalents thereof shall include all those described in the summary, brief description of the drawings, detailed description, abstract, and claims themselves.
The term an “optical fiber” (or laser active fiber) as used herein refers to a flexible, transparent fiber made of an optically transmissive material, such as glass (silica) or plastic, which functions as a waveguide, or “light pipe”, to transmit light between the two ends of the fiber.
The term “porous attenuating member” as used herein shall mean an attenuating member constructed of a rigid member or semi-rigid member having openings therein. Examples of a rigid member and a semi-rigid member include a member constructed of coils, braids, laser-cut tubing, reinforced polymer extrusions, patterned plastics, metals and ceramics. Specific materials used to construct such rigid member and a semi-rigid member may include nitinol (which is a nickel-titanium alloy), stainless steel, titanium, silver, aluminum, cobalt, chromium, nylon, pebax, silicone, urethane, polyethylene and derivatives, nylons, polytetrafluoroethylene and derivatives, polyethylene terephthalate, polypropylene, poly(ether ether ketone), hydroxyapatite, alumina, tricalcium phosphate, silicates or other biocompatible metals, ceramics or polymers. Possible configurations for the porous attenuating member include, but are not limited to, spiral cuts, interrupted spiral cut, honeycomb, lattice structures as found commonly in vascular stents, slots, offset slots, helices, slits that are either longitudinal, radial, circumferential, or a combination thereof, openings that are shaped cutouts. The scope of this disclosure also encompasses the “porous attenuating member” being constructed of a flexible structure and/or a radial flexible structure, although it may be preferable for the attenuating to be constructed of a rigid member or semi-rigid member.
The term “rigid structure” as used herein shall mean a structure that is able to bend or otherwise conform to the shape of the vasculature as it passes therethrough but is substantially unable to expand and/or contract in the radial direction upon a laser induced pressure wave passing therethrough.
The term “semi-rigid structure” as used herein shall mean a structure that is partly rigid with an additional degree of flexibility as it passes through the vasculature but is substantially unable to expand and/or contract in the radial direction upon a laser induced pressure wave passing therethrough.
The term “sheath” as used herein generally refers to a tube that can be inserted into a body cavity duct, lumen, or vessel, such as the vasculature system that allows for the introduction of catheters and the introduction of fluid along its length. An example of a catheter that can be introduced into a sheath is a laser catheter. An example of fluid that can be introduced into a sheath is an absorptive fluid such as contrast. The sheath can have a closed end or an open end. Because the sheath is a tube that can be inserted into a body cavity, duct, lumen, or vessel, such as the vasculature system, the sheath may also be considered a catheter. Accordingly, a catheter, such as a laser catheter, can be introduced into another catheter.
The term “therapeutic agent” as used herein generally refers to any known or hereafter discovered pharmacologically active agent that provides therapy to a subject through the alleviation of one or more of the subject's physiological symptoms. A therapeutic agent may be a compound that occurs in nature, a chemically modified naturally occurring compound, or a compound that is chemically synthesized. The agent will typically be chosen from the generally recognized classes of pharmacologically active agents, including, but not necessarily limited to, the following: analgesic agents; anesthetic agents; antiarthritic agents; respiratory drugs, including antiasthmatic agents; anticancer agents, including antineoplastic drugs; anticholinergics; anticonvulsants; antidepressants; antidiabetic agents; antidiarrheals; antihelminthics; antihistamines; antihyperlipidemic agents; antihypertensive agents; anti-infective agents such as antibiotics and antiviral agents; antiinflammatory agents; antimigraine preparations; antinauseants; antiparkinsonism drugs; antipruritics; antipsychotics; antipyretics; antispasmodics; antitubercular agents; antiulcer agents; antiviral agents; anxiolytics; appetite suppressants; attention deficit disorder (ADD) and attention deficit hyperactivity disorder (ADHD) drugs; cardiovascular preparations including calcium channel blockers, CNS agents; beta-blockers and antiarrhythmic agents; central nervous system stimulants; cough and cold preparations, including decongestants; diuretics; genetic materials; herbal remedies; hormonolytics; hypnotics; hypoglycemic agents; immunosuppressive agents; leukotriene inhibitors; mitotic inhibitors; restenosis inhibitors; muscle relaxants; narcotic antagonists; nicotine; nutritional agents, such as vitamins, essential amino acids and fatty acids; ophthalmic drugs such as antiglaucoma agents; parasympatholytics; psychostimulants; sedatives; steroids; sympathomimetics; tranquilizers; and vasodilators including general coronary, peripheral and cerebral.
The term “vapor bubble” as used herein is a gaseous cavity created within a liquid.
The terms “vasculature” and “vascular” as used herein refer to any part of the circulatory system of a subject, including peripheral and non-peripheral arteries and veins. Vasculature can be comprised of materials such as nucleic acids, amino acids, carbohydrates, polysaccharides, lipids fibrous tissue, calcium deposits, remnants of dead cells, cellular debris and the like.
The term “vascular occlusion” or “occlusion” refers to buildup of fats, lipids, fibrin, fibro-calcific plaque, thrombus and other atherosclerotic tissue within the lumen or within the intima of an artery that either narrows or completely obstructs the inner lumen the artery thereby restricting or blocking normal blood flow through the artery segment. The occlusion may partially or totally occlude the vasculature. Accordingly, the term “vascular occlusion” or “occlusion” shall include both a total occlusion and a partial occlusion. Alternatively, a vascular occlusion or occlusion may also be referred to as a vascular obstruction (or obstruction) or a vascular restriction (or restriction). A vascular obstruction may, therefore, be referred to as a total obstruction or a partial obstruction, and a vascular restriction may be referred to as a total restriction or a partial restriction.
It should be understood that every maximum numerical limitation given throughout this disclosure is deemed to include each and every lower numerical limitation as an alternative, as if such lower numerical limitations were expressly written herein. Every minimum numerical limitation given throughout this disclosure is deemed to include each and every higher numerical limitation as an alternative, as if such higher numerical limitations were expressly written herein. Every numerical range given throughout this disclosure is deemed to include each and every narrower numerical range that falls within such broader numerical range, as if such narrower numerical ranges were all expressly written herein.
The preceding is a simplified summary of the disclosure to provide an understanding of some aspects of the disclosure. This summary is neither an extensive nor exhaustive overview of the disclosure and its various aspects, embodiments, and configurations. It is intended neither to identify key or critical elements of the disclosure nor to delineate the scope of the disclosure but to present selected concepts of the disclosure in a simplified form as an introduction to the more detailed description presented below. As will be appreciated, other aspects, embodiments, and configurations of the disclosure are possible utilizing, alone or in combination, one or more of the features set forth above or described in detail below.
The accompanying drawings are incorporated into and form a part of the specification to illustrate several examples of the present disclosure. These drawings, together with the description, explain the principles of the disclosure. The drawings simply illustrate preferred and alternative examples of how the disclosure can be made and used and are not to be construed as limiting the disclosure to only the illustrated and described examples. Further features and advantages will become apparent from the following, more detailed, description of the various aspects, embodiments, and configurations of the disclosure, as illustrated by the drawings referenced below.
The present disclosure relates generally to the use of medical devices for the treatment of vascular conditions. In particular, the present disclosure provides materials and methods for using laser-induced pressure waves to disrupt vascular blockages and to deliver therapeutic agents to the blockage area.
Referring to
Laser 130 is connected with the proximal end of a laser energy delivery system 120, illustratively a laser catheter 170 via coupler 140. Laser catheter 170 includes one or more optical energy transport devices which receive laser energy from laser 130 and transports the received laser energy from a first, proximal end 124 of laser energy catheter 170 towards a second, distal end 126 of laser catheter 170. The distal end of catheter 170 may be inserted into a vessel or tissue of a human body 110. In some embodiments, system 100 employs a plurality of light guides as the optical energy transport devices, such as optical fibers, that guide laser light from laser 130 through catheter 170 toward a target area in human body 110.
Exemplary laser catheter devices or assemblies may include laser catheters and/or laser sheaths. Examples of laser catheters or laser sheath are sold by The Spectranetics Corporation under the tradenames ELCA™ and Turbo Elite™ (each of which is used for coronary intervention or peripheral intervention, respectively, such as recanalizing occluded arteries, changing lesion morphology, and facilitating stent placement) and SLSII™ and GlideLight™ (which is used for surgically implanted lead removal). The working (distal) end of a laser catheter typically has a plurality of laser emitters that emit energy and ablate the targeted tissue. The opposite (proximal) end of a laser catheter typically has a fiber optic coupler 140 and an optional strain-relief member 124. The fiber optic coupler 140 connects to a laser system or generator 130. One such example of a laser system is the CVX-300 Excimer Laser System, which is also sold by the Spectranetics Corporation.
The laser controller 165 of
A laser source of laser 130 is operatively coupled to laser controller 165. Laser source is operative to generate a laser signal or beam and provide the laser signal through a fiber optic bundle of catheter 170 to the human. Fiber optic bundle serves as delivery devices for delivering the laser signal to the target area of the human body 110.
Referring to
The inner sheath 184, which is constructed of a biocompatible polymer has one or more lumens, which are used to deliver a liquid medium to the cavity, thereby partially or completely filling the cavity with the liquid medium. The liquid medium is introduced to the catheter 170 through one or more liquid medium ports (not shown) in fluid communication with the one or more lumens 190 (not shown) within the inner sheath 184 and disposed about the outer sheath 182. The liquid medium ports may also serve as a means for removing the liquid medium from the catheter 170.
The liquid medium is configured to absorb light energy and thereby produce laser-induced pressure waves in the liquid medium. The laser-induced pressure wave compresses the fluid surrounding its origin, thereby generating a vapor bubble. As the laser-induced pressure wave propagates away from its origin, the fluid surrounding the vapor bubble displaces inwardly, collapsing the vapor bubble and creating a cavitation event. The vapor bubble and subsequent cavitation event(s) are byproducts of the laser-induced pressure wave. And the subsequent cavitation event(s) produce additional resultant pressure waves that are transmitted to the tip 180 and/or the outer sheath 182 to disrupt a vascular occlusion.
Liquid medium can include contrast medium, including for example, iodine-containing contrast medium or gadolinium contrast medium, as well as contrast solutions comprising dye(s) and/or particle(s). Additionally, any liquid medium can be used, as long as the liquid medium is coupled with a light source, such as emitters coupled to the one or more optical fibers, which emits light at a suitable wavelength such that the liquid absorbs the light, produces laser-induced pressure waves, vapor bubbles, and cavitation events that produce additional resultant pressure waves. In some cases, the liquid medium can be contrast medium (for example, iodine-containing contrast medium or gadolinium contrast medium) and/or the liquid medium can be a contrast solution comprising a biocompatible fluid (for example, saline) in which a contrast dye(s) or particle(s) have been mixed at various concentrations.
As mentioned above, one or more optical fibers 186 are disposed within the inner sheath 184 extending from a proximal portion of the inner sheath 184 to the distal end of the inner sheath 184 and into the cavity. The proximal end of the one or more optical fibers is coupled to the laser generator 130. The distal end(s) of the one or more optical fibers 186 are proximate, at, or distal the distal end of the inner sheath 184. Again, one or more emitters are disposed at the distal end of the one or more optical fibers 186. The emitter(s) are in direct contact with the liquid medium, such that when laser light energy is emitted from the emitter(s), the liquid medium absorbs the emitted light, which in turn produces laser-induced pressure waves and generates vapor bubbles and cavitation events that produce additional pressure waves.
To treat a subject having a vascular occlusion, the tip 180 of the catheter 170 is positioned adjacent to the vascular occlusion. When the laser system 130 is activated, light energy travels through one or more optical fibers until the light energy is released from the emitter. As the liquid medium absorbs the light energy, laser-induced pressure waves are produced. Additionally, the liquid medium rapidly displaces outwards and inwards, creating vapor bubbles. The energy produced by the laser-induced pressure waves is captured within the cavity and converted to mechanical energy via moving the tip and/or transferred to the vascular occlusion through the tip. The transfer of the energy produced by the laser-induced pressure waves to the vascular occlusion is sufficient to disrupt vascular occlusion, particularly the calcified and/or fibrous (for example, calcium deposits) portions of a total occlusion. It is desirable for the mechanical energy created at the tip by the laser-induced pressure waves and resulting fluid displacement to be transferred to the occlusion. Accordingly, when the energy produced by the laser-induced pressure waves is captured within the cavity, it is desirable for the forces generated by the laser-induced pressure waves to propagate longitudinally, including in a forward (that is, parallel with the vessel) direction, thereby increasing the tip's ability to disrupt, destroy and/or penetrate the vascular occlusion. That is, as the laser-induced pressure waves are produced, the tip of the catheter rapidly moves (translates) forwards and backwards towards and away from, respectively, the occlusion. Pressure waves produced in this manner can also be used to increase vessel compliance prior to performing another procedure, such as a traditional balloon angioplasty or drug eluting balloon treatment.
In order to facilitate the direction in which the forces that are produced by the laser-induced pressure waves translate into the movement of the tip in a forward/backward longitudinal direction, the outer sheath 182 is not only flexible, but the outer sheath 182 also has the ability to expand and contract in a longitudinal direction. One example of such an outer sheath 182 includes a slotted or laser-cut hypotube constructed of a biocompatible material, such as stainless steel, or a biocompatible polymer. The hypotube has spring-like characteristics, which allow it to expand and contract in a longitudinal direction. Specifically, the slotted or laser cut pattern in the hypotube allows it to expand and contract. Another example of the outer sheath 182 may include of one or more spirally wound wires, thereby creating a coiled sheath, which also has the ability to expand and contract in a longitudinal direction.
The transfer of the energy produced by the creating a laser-induced pressure wave to the vascular occlusion and/or to the walls of the vessel is sufficient to disrupt intraluminal calcium as well as calcium within the tissue of the blood vessel, vascular occlusion (for example, calcium deposits). The forces generated by the laser-induced pressure wave can propagate radially, including in forward (that is, parallel to the vessel), upward (that is, perpendicular to the vessel), and backward (that is, proximally) directions. Laser-induced pressure waves produced in this manner can also be used to increase vessel compliance prior to performing another procedure, such as a traditional balloon angioplasty, drug-eluting balloon angioplasty and/or stent placement. That is, the laser-induced pressure wave disruption of the intraluminal calcium and/or calcium within the tissue of the blood vessel and the vascular occlusion, can improve the vasculature's ability to absorb drugs, particularly when such drugs are applied with a drug eluting balloon.
Referring again to
The present disclosure envisions a two-piece catheter system or kit 300. Referring to
Referring to
Continuing to refer to
Referring to
Once the entire vascular occlusion has been traversed by the laser catheter 170, the opening created by the laser catheter 170 should be large enough to translate the sheath 250 distally and through the vascular occlusion. At this point, both the distal end of the sheath 250 and the distal end of the laser catheter 170 should be distal of the vascular occlusion. At this point, referring to
To ensure that the majority of the remainder of the vascular occlusion 175″ is disrupted, and if desired, disrupt the intraluminal calcium and/or calcium within the tissue layers (e.g., medial layer) of the blood vessel, and the vascular occlusion, the laser catheter 170 may be repeatedly translated distally and proximally within the sheath 250. As discussed above, disruption of the intraluminal layer and/or tissue layers (e.g., medial layer) of the blood vessel and the vascular occlusion, can improve the vasculature's ability to absorb drugs, particularly when such drugs are applied with a drug eluting balloon. Also, it is contemplated that prior to, during and/or after any step in the process outlined in
Laser-induced pressure waves generally have different characteristics in comparison to ultrasound. Ultrasound typically consists of periodic oscillations with limited bandwidth. Laser-induced pressure waves are single, mainly positive pressure pulses that are followed by comparatively small tensile wave components. Ultrasound applies an alternating high frequency load to tissue, with a frequency range of several megahertz, and can thus lead to heating, tissue tears and cavitation at high amplitudes. The effect of laser-induced pressure waves in comparison, however, largely involves radially directed energy, as described above, enabling the treatment of deep tissue as well as adjacent tissue with enhanced sensitivity.
The ability of the catheter of the present disclosure to generate laser-induced pressure waves for treating a vascular occlusion in a subject involves the suitable coupling of the light system and the liquid medium. Any wavelength of light can be used, including but not limited to, laser light, visible light, ultraviolet light and infrared light, as long as the light being emitted is coupled with a liquid medium capable of absorbing the light and producing laser-induced pressure waves. Additionally, any liquid medium can be used, as long as the liquid medium is coupled with a light source that emits light at a suitable wavelength such that the liquid absorbs the light and creates laser-induced pressure waves and/or vapor bubbles. In some cases, the liquid medium can be contrast medium (for example, iodine-containing contrast medium or gadolinium contrast medium) and/or the liquid medium can be a contrast solution comprising a biocompatible fluid (for example, saline) in which a contrast dye(s) or particle(s) have been mixed at various concentrations.
The force amplitude generated by the laser-induced pressure waves depends in part on the degree of absorption of the light energy by the liquid medium as well as total energy deposited by the light source. Generally, the greater the absorption of the light energy by the liquid medium, the greater the force generated by the laser-induced pressure waves. Also, the greater the amount of the light energy delivered to the liquid medium, the greater the force generated by the laser-induced pressure waves. For example, an excimer laser typically emits laser light at a wavelength of about 308 nanometers at pulse durations between about 120 nanoseconds and about 140 nanoseconds, at frequencies between about 25 pulses per second to about 80 pulses per second, and with a total energy output between about 1 to about 100 millijoules. In some cases, however, total energy output of a laser light system can range from greater than 0 to about 300 mJ. When emitted within contrast medium, such as iodine-containing contrast medium or gadolinium contrast medium, there will be a very high degree of absorption by the contrast medium, thus creating laser-induced pressure waves with sufficient force to treat a vascular occlusion in a subject.
Light energy can be emitted at any suitable wavelength capable of generating laser-induced pressure waves. Light energy can be emitted between about 1 nanometer and about 1 millimeter. In some cases, light can be emitted from about 10 nanometers to about 5000 nanometers. In some cases, light can be emitted from about 100 nanometers to about 1000 nanometers. In some cases, light can be emitted from about 250 nanometers to about 750 nanometers. In some cases, light can be emitted from about 300 nanometers to about 600 nanometers. In still other cases, light can be emitted from about 300 nanometers to about 350 nanometers.
Light energy can be emitted at any suitable pulse duration capable of generating laser-induced pressure waves. In some cases, light can be emitted at pulse durations between about 1 femtosecond to about 1 second. In some cases, light can be emitted at pulse durations between about 10 nanoseconds to about 500 nanoseconds. In some cases, light can be emitted at pulse durations between about 100 nanoseconds to about 150 nanoseconds. In still other cases, light can be emitted at pulse durations between about 120 nanoseconds and about 140 nanoseconds.
Light energy can be emitted at any suitable pulse repetition frequency (PRF), or pulses per second, capable of generating vapor bubbles and producing resultant pressure waves that propagate through the surrounding vasculature. In some cases, light can be pulsed at a frequency of between about 1 pulse to about 5000 pulses per second. In some cases, light can be pulsed at a frequency of between about 10 pulses to about 2500 pulses per second. In some cases, light can be pulsed at a frequency of between about 10 pulses to about 1500 pulses per second. In some cases, light can be pulsed at a frequency of between about 100 pulses to about 1000 pulses per second. In other cases, light can be pulsed at a frequency of between about 50 pulses to about 500 pulses per second. In other cases, light can be pulsed at a frequency of between about 50 pulses to about 150 pulses per second. In other cases, light can be pulsed at a frequency of between about 50 pulses to about 100 pulses per second. In still other cases, light can be pulsed at a frequency of between about 25 pulses to about 80 pulses per second.
The total number of pulses administered during a particular treatment period depends on a variety of factors, including patient characteristics, the type of condition being treated, and the specific characteristics of the vascular occlusion, as one of ordinary skill in the art would readily appreciate based on the present disclosure. In some cases, the total number of pulses administered during a treatment period can range from a single pulse to any number of pulses generated in a 10 second treatment period, a 15 second treatment period, a 20 second treatment period, a 25 second treatment period, a 30 second treatment period, up to a 1 minute treatment period. Treatment periods can be repeated depending on the extent of the vascular occlusion remaining after initial treatment.
For example, a generator and/or one or more emitters may be configured to emit laser light energy at wavelengths of between about 150 nanometers to about 400 nanometers, at pulse durations between about 1 femtosecond to about 1 second, and at frequencies between about 1 pulse per second to about 5000 pulses per second. In some cases, the generator and/or the emitter(s) may be configured to emit laser light energy at wavelengths of between about 400 nanometers to about 800 nanometers, at pulse durations between about 1 femtosecond to about 1 second, and at frequencies between about 1 pulse per second to about 5000 pulses per second. In other cases, the generator and/or the emitter(s) may be configured to emit laser light energy at wavelengths of between about 800 nanometers to about 3,000 nanometers, at pulse durations between about 1 femtosecond to about 1 second, and at frequencies between about 1 pulse per second to about 5000 pulses per second. In other cases, the generator and/or the emitter(s) may be configured to emit laser light energy at wavelengths of between about 3,000 nanometers to about 12,000 nanometers, at pulse durations between about 1 femtosecond to about 1 second, and at frequencies between about 1 pulse per second to about 5000 pulses per second. In other cases, the generator and/or the emitter(s) may be configured to emit laser light energy at wavelengths of between about 300 nanometers to about 360 nanometers, at pulse durations between about 1 femtosecond to about 1 second, and at frequencies between about 1 pulse per second to about 5000 pulses per second.
The degree of force generated by the laser-induced pressure waves can be modulated by using lasers that produces laser light energy at different wavelengths and at different pulse durations, as would be appreciated by one of ordinary skill in the art based on the present disclosure. For example, different degrees of force may be required to break apart a vascular occlusion, as compared to the degree of force required to deliver a therapeutic agent to vascular tissue. In some embodiments, a laser having a holmium source, referred a Holmium laser, can emit laser light energy at a wavelength of about 2,100 nanometers (nm) and can be coupled with various light absorbing materials, including an aqueous or saline-based medium, to treat a vascular occlusion in a subject.
Several other additional sources of laser light energy can be paired with corresponding light absorbing materials to generate laser-induced pressure waves to treat a vascular occlusion. For example, YAG crystal lasers can produce wavelengths of infrared light, which is highly absorptive in aqueous solutions. Aqueous solutions can be used as light absorbing material or medium to generate laser-induced pressure waves. Aqueous solutions include, but are not limited to, saline, dextrose, radio-opaque contrast, lactated ringer's, and electrolyte solutions. In some cases, YAG wavelengths can be doubled to generate visible spectrum light of 532 nm wavelength. Materials or medium capable of absorbing light of this wavelength include, but are not limited to, gold nanospheres, nitrite solutions, potassium permanganate solutions, copper salts, aluminum solutions, aluminon, ammonia salts, and dyes such as hemotoxylin and propidium iodide. Light absorbing materials such as these can be part of a solution, such as an aqueous solution as described above, and/or they can be applied as coatings on various surfaces within a device.
In some embodiments, a Holmium YAG laser can emit laser light energy at a wavelength of about 2,120 nm and can be coupled with various light absorbing materials, including an aqueous or saline-based medium, to treat a vascular occlusion in a subject. In some embodiments, a thulium laser, such as a Thulium YAG laser, can emit laser light energy at a wavelength of about 2,013 nm and can be coupled with various light absorbing materials, including an aqueous or saline-based medium, to treat a vascular occlusion in a subject. In some embodiments, a thulium laser, such as a Thulium Fiber laser, can emit laser light energy at a wavelength of about 1,908 nm and can be coupled with various light absorbing materials, including an aqueous or saline-based medium, to treat a vascular occlusion in a subject. In some embodiments, an Nd-YAG laser can emit laser light energy at a wavelength of about 1,064 nm and can be coupled with various light absorbing materials to treat a vascular occlusion in a subject. In some embodiments, a doubled YAG laser can emit laser light energy at a wavelength of about 532 nm and can be coupled with various light absorbing materials to treat a vascular occlusion in a subject. In some embodiments, an alternative band YAG laser can emit laser light energy at a wavelength of about 1,319 nm and can be coupled with various light absorbing materials to treat a vascular occlusion in a subject. In still other embodiments, an Er-YAG laser can emit laser light energy at a wavelength of about 2,940 nm and can be coupled with various light absorbing materials to treat a vascular occlusion in a subject.
Carbon dioxide (CO2) lasers can emit infrared light that is highly absorptive in aqueous solutions. CO2 lasers are common surgical lasers and are highly absorptive in tissues due to their high water content. Light absorbing materials that can be coupled with CO2 lasers that emit infrared light, such as light emitted at a 10.6 micron wavelength, to generate laser-induced pressure waves include, but are not limited to, aqueous solutions such as saline, dextrose, radio-opaque contrast, lactated ringer's, and electrolyte solutions.
Nitrogen lasers can be used to produce low frequency, high energy laser pulses. Nitrogen lasers can emit light in the UV spectrum can emit laser light energy at a wavelength of about 337 nm and can be coupled with various light absorbing materials to generate laser-induced pressure waves, including but not limited to, radio-opaque contrast as well as metals and oxides such as aluminum, silver, gold, copper, nickel, cerium, zinc, titanium, and dyes such as hydroxycoumarin and aminocoumarin.
Other medically useful lasers that can be used to generate a laser-induced pressure wave to treat a vascular occlusion include Ti-Sapphire lasers, which can emit laser light energy at wavelengths of about 800 nm; Ruby lasers, which can emit laser light energy at wavelengths of about 694 nm; and Alexandrite lasers, which can emit laser light energy at about 755 nm. These medical lasers emit laser light energy in the near infrared light spectrum, and can be used for laser-induced pressure wave generation. Light absorbing material or medium that can be coupled with these laser include, but are not limited to, dyes and colorants which could be used in solution, suspension, or coating on another material or surface within a device. Various materials capable of absorbing laser light energy in these wavelengths include aqueous copper, copper salts, and cupric sulfate, and materials such as fluorophores that are used in fluorescent microscopy (for example, methylene blue).
Dye lasers can also be used to generate laser-induced pressure waves to treat a vascular occlusion. In some cases, dye lasers can be tuned to output a specific wavelength of light in the visible spectrum, which can allow for the optimization of the laser for a certain light absorbing material, as an alternative or in addition to, using a material which is highly absorptive of a specific wavelength of light. In this way, the light absorbing material can be any of the previously mentioned materials, as well as dyes, colorants, and visible light chromophores.
For certain applications, it may be desirable to increase the amount and/or the size of vapor bubbles produced along with a laser-induced pressure wave that is generated by emitting laser light energy into a corresponding light absorbing liquid medium. For example, when entering smaller diameter sized blood vessels, the size of the catheter may be limited. In some cases, the force that vapor bubbles exert on tissue (for example, a vascular occlusion) may be proportional to the size of the individual vapor bubbles created, as the bubbles expand and contract after laser light energy is emitted into liquid medium and a pressure wave is generated. That is, the strength of the initial laser-induced pressure wave and/or the size of the vapor bubble may be limited with the use of a non-gas saturated liquid medium. One manner by which the size of individual vapor bubbles can be increased (for example, to impart greater amount of force on a particular tissue) is to saturate the liquid medium with gaseous substances so that the gas within the liquid medium exhibits a higher vapor pressure as compared to that of the liquid medium without such gas. Suitable gaseous substances that may be used to create gas-saturated liquid medium include, but are not limited to, ambient air, carbon dioxide, iodine gas, oxygen, nitrogen, compressed air, nitrous oxide, and combinations of these.
The higher vapor pressure of the gaseous substance added to the liquid medium will cause the gaseous substance to return to a gaseous state faster (under smaller pressure fluctuations) than the liquid medium. In other words, less pressure is required to cause the saturated gaseous substances to come out of solution, resulting in the creation of larger vapor bubbles, and concomitantly, a greater amount of force. In some cases, the use of gas-saturated liquid medium allows for the use of laser light energy at decreased intensities, or decreased pulses or pulse durations, without any accompanying decrease in the overall force generated by the vapor bubbles (as each vapor bubble is larger). This can enhance both the safety and efficacy of the procedure being performed.
The gaseous substances can be imparted to the liquid medium through various means, including under pressure, through mechanical agitation, and/or by bubbling the gas into the liquid medium. In some cases, gas-saturated liquid medium can be prepared prior to a procedure and then delivered to the distal end of a catheter prior to performing the procedure. Additionally or alternatively, gaseous substances can be delivered into that liquid medium that is already present in the catheter.
The gases and/or gaseous substances may be dissolved and quantified by the amount of gases present in a 1 kg of the liquid medium. The maximum amount of gas that will dissolve in the liquid medium is dependent on the solubility of the particular gas in that liquid medium, the pressure, and the temperature as described by Henry's law of gas solubility. For example, carbon dioxide may be dissolved into water at a concentration of 1.25 g/kg of water or less at 30 degrees C. under atmospheric pressure. And upon dissolving carbon dioxide into water or saline, an overall concentration between 0.25-3.5 g/kgH2O is produced. The concentrations of other dissolved gases in a kilogram of liquid medium ranges from 1 mg-1 g/kg for iodine, 5-80 mg/kg for oxygen, 5-40 mg/kg for nitrogen, 5-500 mg/kg for room air, and 0.1-4 g/kg for nitrous oxide.
The gases and/or gaseous substances may be dissolved in quantities above the theoretical limit, which is known as super saturation. The theoretical limit is described by Henry's law as mentioned previously. By dissolving the gases under increased pressure or decreased temperature and then returning it to normal atmospheric conditions, it is possible to dissolve a larger quantity of gas then is possible at atmospheric conditions. For example, 2.5 g of carbon dioxide may be dissolved into 30 degrees C. water under 2 atm of pressure, and then returned to atmospheric pressure. For any dissolved gas, the saturation percentage is defined by the concentration of gas over the theoretical maximum concentration. For any of the previously mentioned gases in a supersaturated solution, the saturation percentage can range from 100-300 percent.
The use of a gas saturated liquid medium or super saturated liquid medium may also increase the initial laser-induced pressure wave caused by the interaction of the laser light and the liquid medium. That is, the gas saturated liquid medium or super saturated liquid medium may contain larger potential energy, which when activated by the laser light, may create a larger initial laser-induced pressure wave in comparison to a laser-induced pressure wave created by the interaction of laser light and a non-gas saturated liquid medium.
Additionally or alternatively, methods of the present disclosure also include activating at least one proximal laser emitter enclosed within the sheath assembly to send pulses of laser light energy through the liquid medium and propagating laser-induced pressure waves to assist in stent deployment. Pressure waves generated from vapor bubbles can assist in seating or expanding the stent to its full diameter as part of a medical procedure.
As discussed above, activating one or more emitters and transmitting pulses of light energy into the liquid medium produces vapor bubbles. Upon emitting light from an emitter, such as a laser catheter, within a sheath that contains an absorptive liquid medium, the vapor bubbles may be produced within the interior of the sheath and/or exterior to the sheath. Assuming that the vapor bubbles are created on the interior of the sheath, it may be desirable to limit some or all of the potential expansion of the relevant portion of the sheath caused by the vapor bubbles. That is, it may be desirable to reduce or prevent the sheath's ability to expand and contract upon creation of the vapor bubbles therein so as to reduce or prevent the sheath from applying a hydraulic force or pressure to the vascular occlusion and/or to the walls of the vessel. Also, assuming that the vapor bubbles are created on exterior of the sheath within the vessel wall, it may be desirable to reduce and/or prevent the formation of such vapor bubbles so as to reduce or prevent the cavitation event and the formation of the vapor bubbles themselves from applying a hydraulic force or pressure to the vascular occlusion and/or to the walls of the vessel.
Referring to
The attenuating member 524″ has two purposes. One purpose is to reinforce the sleeve 522″ and/or the sheath 250″, and the other purpose is to reduce the size or prevent the likelihood formation of vapor bubbles exterior of the attenuating member 524″, the sleeve 522″ and/or the sheath 250″. Regarding the reinforcing the sleeve 522″, coupling the attenuating member 524″ with the sleeve 522″ may reduce or prevent the sheath's ability to expand and contract upon creation of the vapor bubbles therein so as to reduce or prevent the sleeve 522″ from applying a hydraulic force or pressure to the vascular occlusion and/or to the walls of the vessel. Reinforcing the sleeve 522″ may minimize and/or prevent the sleeve from bulging, splitting, or delaminating (in the event the sleeve comprises multiple layers), as well as minimize and/or prevent a hole from forming within the sleeve. In the event of one or more occurrences, the difficulty of subsequent translation of the sleeve through the patient's vasculature and/or translation relative to the laser catheter may be increased.
Both the attenuating member 524″ and the sleeve 522″ are constructed of biocompatible materials. Coupling the attenuating member 524″ with the sleeve 522″ forms a rigid or semi-rigid structure within the sheath 250″ such that it applies a small hydraulic force or it does not apply a hydraulic force to the vascular occlusion and/or to the walls of the vessel upon formation of vapor bubbles therein. It may be desirable that the majority or only force(s) applied to the vascular occlusion and/or to the walls of the vessel are a result of the laser-induced pressure waves that pass through the 250″, thereby allowing more precise control over the laser-induced pressure waves.
Regarding the other purpose of the attenuating member 524″, which is to reduce or prevent the formation of vapor bubbles exterior of the attenuating member 524″, the sleeve 522″ and/or the sheath 250″ and continuing to refer to
The attenuating member's ability to reduce or prevent the formation of vapor bubbles exterior of the attenuating member 524″, the sleeve 522″ and/or the sheath 250″ potentially reduces the existence and/or the size of the vapor bubbles formed on the exterior of the attenuating member 524″, the sleeve 522″ and/or the sheath 250″, which in turn reduces the likelihood that vapor bubbles will be created and expand and contract between the attenuating member 524″, the sleeve 522″ and/or the sheath 250″ and the vasculature wall. And reducing or preventing expansion and contraction of vapor bubbles between the sleeve 522″, and/or the sheath 250″, and the vasculature wall prevent or reduce the likelihood that a hydraulic force or pressure will be applied to the vascular occlusion and/or to the walls of the vessel, thereby preventing and/or minimizing potential damage to the vasculature itself.
Regarding the attenuating member's ability to reinforce the sleeve 522″ and/or the sheath 250″, the attenuating member 524″ may reduce or prevent the sleeve's ability and/or the sheath's ability to expand and contract upon creation of the vapor bubbles therein. Reducing the sleeve's ability and/or the sheath's ability to expand and contract upon the formation of vapor bubbles therein, reduces or prevents the sleeve 522″ and/or the sheath 250″ from applying a hydraulic force or pressure to the vascular occlusion, restriction and/or to the walls of the vessel.
The openings 526″ in the attenuating member 524″ depicted in
Referring to
Continuing to refer to
Referring to
Referring to step 650 of
To ensure that the majority of the remainder of the vascular occlusion 175′ is disrupted, and if desired, disrupt the intraluminal layer and/or the tissues of the blood vessel and the vascular occlusion, the laser catheter 170 may be repeatedly translated distally and proximally within the sheath 250. As discussed above, disruption of the intraluminal layer and/or tissues of the blood vessel and the vascular occlusion, can improve the vasculature's ability to absorb drugs, particularly when such drugs are applied with a drug eluting balloon. Also, it is contemplated that prior to, during and/or after any step in the process outlined in
As discussed above, transmitting pulses of light energy from an emitter into a liquid medium creates laser-induced pressure waves and/or vapor bubbles and cavitation events resulting in additional pressure waves that disrupt at least a portion of a vascular occlusion. The catheter may include a guidewire lumen through which a guidewire can pass and cross the vascular occlusion. It may also be desirable to excite and vibrate the guidewire to increase the guidewire's ability to pierce and cross the vascular occlusion. Accordingly, the present disclosure also contemplates directing the laser light energy emitted by the emitter into the liquid medium in a direction which causes the liquid medium to propagate pressure waves toward the guidewire lumen and/or guidewire such that the pressure waves excite and vibrate the guidewire.
In some embodiments, the devices and methods of the present disclosure can also be used deliver laser-induced pressure waves to ablate a vascular occlusion using a substantially solid light absorbing material instead of liquid medium. In some circumstances, pairing a laser that emits a specific wavelength of light with a light absorbing material designed to absorb light at that wavelength can significantly increase the energy efficiency of the resultant laser-induced pressure waves produced by the reaction. The use of such pairings can ultimately reduce the energy input required to treat a vascular occlusion, which can increase the safety of the procedure and reduce costs. For example, the catheters according to embodiments of the present disclosure can be filled with air or a substantially inert liquid medium (for example, saline) instead of contrast medium, which can significantly reduce the amount and size of vapor bubbles produced along with the laser-induced pressure waves. Because the laser-induced pressure waves can propagate outside of the catheter to ablate a vascular occlusion, it can be advantageous in some circumstances to reduce (for example, by filling the catheter with saline) or eliminate (for example, by filling the catheter with air or inert gas) the production of vapor bubbles. In other cases, liquid medium delivered to the distal end of the catheter can be pre-treated to remove the amount of gas dissolved in it using methods known to one of ordinary skill in the art based on the present disclosure, as this can also reduce the amount of vapor bubbles generated along with the laser-induced pressure waves.
Suitable light absorbing material can be any agent capable of absorbing light energy and producing a laser-induced pressure wave. For example, the light absorbing material can contain an aromatic hydrocarbon with iodine bonded to it, such as iodinated x-ray contrasts. Low osmolar, non-ionic, iodinated, and radio-opaque contrasts are also suitable light absorbing materials that can be used to produce laser-induced pressure waves. Other light absorbing materials include, but are not limited to, iodinated contrasts such as Diatrizoic acid, Metrizoic acid, lodamide, lotalamic acid, loxitalamic acid, loglicic acid, Acetrizoic acid, locarmic acid, Methiodal, Diodone, Metrizamide, lohexol, loxaglic acid, lopamidol, lopromide, lotrolan, loversol, lopentol, lodixanol, lomeprol, lobitridol, loxilan, lodoxamic acid, lotroxic acid, loglycamic acid, Adipiodone, lobenzamic acid, lopanoic acid, locetamic acid, Sodium iopodate, Tyropanoic acid, Calcium iopodate, lopydol, Propyliodone, lofendylate, Lipiodol, non-iodinated contrasts such as Barium sulfate, MRI contrast agents such as Gadobenic acid, Gadobutrol, Gadodiamide, Gadofosveset, Gadolinium, Gadopentetic acid, Gadoteric acid, Gadoteridol, Gadoversetamide, Gadoxetic acid, Ferric ammonium citrate, Mangafodipir, Ferumoxsil, and Ferristene Iron oxide nanoparticles, Perflubron, Glucose and other carbohydrates, Albumen and other proteins, Nitroglycerin or other vasodilators, Hydrocarbons such as Oils, Alcohols, or other organic functional groups (Amines, Alkanes, Carboxyl, and the like), blood/tissue products such as Platelet Rich Plasma (PRP), packed red cells, plasma, platelet, fat, Charcoal, biocompatible materials such as stainless steel, biopolymers, and bioceramics, or other pharmacological agents which contain a combination of aromatic carbon rings and functional groups such as Salicylic acid, Acetylsalicylic acid, Methyl salicylate, Mesalazine, Aspirin, Acetaminophen, Ibuprofen, Clopidogrel, or other pharmacological and/or biological agents which may be compatible with the medical procedures described herein.
Suitable light absorbing material can also include those materials capable of absorbing wavelengths in the UV spectrum. For example, light absorbing materials can include, but are not limited to, PABA, Padimate 0, Phenylbenzimidazole sulfonic acid, Cinoxate, Dioxybenzone, Oxybenzone, Homosalate, Menthyl anthranilate, Octocrylene, Octyl methoxycinnamate, Octyl salicylate, Sulisobenzone, Trolamine salicylate, Avobenzone, Ecamsule, 4-Methylbenzylidene camphor, Tinosorb M, Tinosorb S, Tinosorb A2B, Neo Heliopan AP, Mexoryl XL, Benzophenone-9, Uvinul T 150, Uvinul A Plus, Uvasorb HEB, Parsol SLX, or Amiloxate, Silicon and its various atomic structures, Cadmium telluride, Copper indium gallium selenide, Gallium arsenide, Ruthenium metalorganic dye, Polyphenylene vinylene, Copper phthaloncyanine, Carbon fullerenes and derivatives, Carbon compounds such as Graphite, Graphene, Diamond, Charcoal, Titianium and oxides, Nickel and oxides, Gold, Silver, Zinc and oxides, Tin and oxides, Aluminum and oxides, or alloys or ceramics of the preceding metals.
Light absorbing material may be combined with various other compounds to facilitate their attachment to a substrate. For example, light absorbing materials may be combined with various compounds (for example, solubilizing agents) that aid in the generation of a solution or mixture comprising the light absorbing material, which can be used to coat the substrate. In some embodiments, a biodegradable and biocompatible hydrophobic polymer may be used as a light absorbing material. For example, the biodegradable and biocompatible hydrophobic polymer may be poly(glycerol sebacate acrylate) (PGSA), or variations and combinations thereof, which can be crosslinked using ultraviolet light. Ultraviolet light may be emitted from the distal end of a catheter, which may be disposed within or outside of a sheath, to activate the PGSA, for example.
Other light absorbing material can also include agents having adhesive-like properties, and in some cases, the light absorbing properties of these agents can be in addition to, or independent of, their use as adhesives. For example, light absorbing materials can include, but are not limited to, cyanoacrylates, bovine serum albumin (BSA)—glutaraldehyde, fibrin sealants, gelatin matrix thrombin, gelatin sponge, oxidized cellulose, collagen sponge, collagen fleece, recombinant factor VIIa, and the like. In some embodiments, the light absorbing material may comprise hydrophobic functional groups, such as hexanoyl (Hx; C6), palmitoyl (Pam; C16), stearoyl (Ste; C18), and oleoyl (Ole; C18 unsaturated) groups, so as to resist being washed out or disengaged from their substrate in predominately aqueous environments (for example, vascular tissue). Such light absorbing materials can include, but are not limited to, 10Ole-disuccinimidyl tartrate, 10Ste-disuccinimidyl, and variations and combinations thereof.
Light absorbing material can be configured to exhibit high absorption of light energy from an emitter. Light energy can be emitted at any suitable wavelength capable of generating laser-induced pressure waves. Light energy can be emitted between about 1 nanometer and about 1 millimeter. In some cases, light can be emitted from about 10 nanometers to about 5000 nanometers. In some cases, light can be emitted from about 100 nanometers to about 1000 nanometers. In some cases, light can be emitted from about 250 nanometers to about 750 nanometers. In some cases, light can be emitted from about 300 nanometers to about 600 nanometers. In still other cases, light can be emitted from about 300 nanometers to about 350 nanometers.
In general, the light absorbing material can be located anywhere within a catheter, so long as it generally intersects with the path of light emitted from the optical fibers. In some embodiments, the light absorbing material may be substantially solid (for example, stable in a generally solid state, such as metals and metal alloys). Substantially solid light absorbing material can be used to construct various portions of the components of the catheter, and/or substantially solid light absorbing material can be used to construct a separate structure that is independent of another catheter component.
In some embodiments, the light absorbing material can be applied to a separate supporting structure (that is, a support structure that is not predominately made of light absorbing material, or a support structure that is not being used as a light absorbing material) and used to generate laser-induced pressure waves using the devices and methods of the present disclosure. In some embodiments, the light absorbing materials are stable only in liquid, gel, or semi-liquid forms. In these embodiments, the light absorbing material can be included as part of a formulation or coating that is suitable for application to a support structure, such as impregnated in hydrogel or other solid support matrix. In some embodiments, the light absorbing materials can be part of a formulation or coating containing other agents that facilitate their placement on and/or adherence to a support structure. For example, solid absorbing materials can be formulated with coating agents, thickening agents, adhesive agents, and/or other pharmaceutical or biological agents that are suitable for use with the devices and methods of the present disclosure.
As discussed above, the present disclosure discusses using a laser catheter to ablate 170 at least a portion of the vascular occlusion or restriction in the vessel of the subject prior to using the combination of the laser catheter 170 (depicted in
As mentioned above, the media 730 is located radially inward of and adjacent to the inner portion of the adventitia 720. Specifically, an external elastic membrane, commonly referred to as the external elastic lamina, 735 separates the media 730 from the adventitia 720. As also mentioned above, the intima 740 is located radially inward of and adjacent to the inner portion of the media 730. An internal elastic membrane 725, commonly referred to as the internal elastic lamina, separates the intima 740 from the media 730.
Referring to
Referring to
Referring to
Referring to
Referring to
The method 900 in
After the vascular occlusion (or a portion thereof) is removed from the vasculature, step 920 may then be performed. Step 920 includes positioning a sheath 250 of the present disclosure over a laser catheter 170 within vasculature of a subject, as depicted in
Once the sheath 250 and laser catheter 170 are disposed adjacent the vascular occlusion, such that the emitters and the attenuating member are axially aligned adjacent the vascular occlusion as depicted in
Activating at least one energy source coupled to at least one emitter of the laser catheter, which is surrounded by the sheath 250, to emit and send pulses of laser light energy into and/or to react with the liquid medium to produce propagating laser-induced pressure waves and disrupt a remaining portion of the vascular occlusion. Disrupting the remaining portion of the vascular occlusion, particularly any calcified portions within the vascular occlusion, produces cracks in the calcified portions and/or reduces the size of the calcified portions because the laser-induced pressure waves disrupt the calcified portions, thereby cracking the calcified portions and/or fragmenting the size of the calcified particles such that the contiguous area is reduced. In some cases, the method 900 may include an additional step (not shown) of activating at least one energy source coupled to at least one emitter enclosed within the sheath to emit and send pulses of laser light energy into and/or to react with the liquid medium to produce propagating laser-induced pressure waves to deliver a therapeutic agent from the sheath to a remaining portion of the vascular occlusion and/or the vascular tissue near the obstruction or restriction.
One of the benefits of the present disclosure is that the catheter 170 and sheath 250 depicted in
Referring again to
To ensure that the majority of the remainder of the vascular occlusion is disrupted, and if desired, disrupt the intraluminal layer and/or tissues of the blood vessel and the vascular occlusion, the laser catheter 170 may be repeatedly translated distally and proximally within the sheath 250, as in step 945 and/or step 955. As discussed above, disruption of the intraluminal layer and/or tissues of the blood vessel and the vascular occlusion, can improve the vasculature's ability to absorb drugs, particularly when such drugs are applied with a drug eluting balloon. Also, it is contemplated that prior to, during and/or after any step in the process outlined in
As discussed above, transmitting pulses of light energy from an emitter into a liquid medium creates laser-induced pressure waves and/or vapor bubbles and additional resultant pressure waves that disrupt at least a portion of a vascular occlusion. The catheter may include a guidewire lumen through which a guidewire can pass and cross the vascular occlusion. It may also be desirable to excite and vibrate the guidewire to increase the guidewire's ability to pierce and cross the vascular occlusion. Accordingly, the present disclosure also contemplates directing the laser light energy emitted by the emitter into the liquid medium in a direction which causes the liquid medium to propagate laser-induced pressure waves toward the guidewire lumen and/or guidewire such that the laser-induced pressure waves excite and vibrate the guidewire.
Although the method illustrated in
Furthermore, a drug eluting (coated) balloon (DEB or DCB) catheter may be used to deliver drugs to the remnants of the vascular occlusion. Disrupting the remaining portion of the vascular occlusion with the laser-induced pressure waves prior to utilizing a DEB may increase the effectiveness of the drugs being applied to the vascular occlusion because the laser-induced pressure waves disrupt calcium formed in the intima layer, as well as in tissues within the blood vessel, thereby creating a pathway for the drug to enter the intima and tissues within the blood vessel and/or vascular occlusion.
The present disclosure also contemplates using the laser-induced sheath with conventional angioplasty balloons, as well as with DEBs. For example, a surgical procedure may include performing an atherectomy with a laser catheter, using the sheath in combination with the laser catheter to treat the calcified portions of the vasculature as set forth in
As discussed above, the laser-induced pressure waves created by the laser catheter and sheath of the present disclosure not only disrupt a vascular occlusion and/or calcium in the intima layer, the laser-induced pressure waves created by the catheter of the present disclosure can also disrupt calcification of the tissues within the vessel wall(s) That is, the laser-induced pressure waves may be used to fracture or modify calcified tissue regardless of whether the vasculature includes an occlusion. For example, patients with medial artery calcification, which is also known as Mönckeberg's sclerosis, could potentially benefit from being treated with the catheter of the present disclosure.
Referring to
Referring to
The combined catheter 170 and sheath 250 of the present disclosure are able to create laser-induced pressure waves, which fracture or disrupt the calcium deposits 1070 in the media 1030 of the arterial wall 1000″ as shown in
Referring to
After locating the calcified portion(s) of the tissue (e.g., media) and/or tissue layers (e.g., media layer) within the vasculature, step 1130 may then be performed. Step 1130 includes introducing to the vasculature a laser catheter of the present disclosure and a sheath of the present disclosure over the laser catheter. Step 1140 includes positioning within the vasculature the sheath and the laser catheter (and optionally the guidewire) such that an attenuating member within the sheath is adjacent the portion of vasculature having the calcification, and the distal end of the laser catheter is disposed within the attenuating member adjacent the vasculature that includes the calcified portion(s). For example, if a clinician uses a laser catheter 170 described herein, which has a guidewire lumen, the laser catheter may be slid over the guidewire and into the vasculature such that the emitter(s) of the laser catheter are positioned adjacent to the vasculature that has the calcification. A sheath 250 of the present disclosure is then slid over the laser catheter 170 to a position within the vasculature such that the attenuating member is adjacent the vasculature that includes the calcified portion(s). Accordingly, the emitter will be disposed within the portion of the sheath comprising the attenuating member.
The method 1100 also includes step 1150, which comprises introducing the liquid medium (for example, contrast medium) having light absorbing material to the distal end of the laser catheter, wherein the laser catheter is disposed within the sheath, and preferably within the portion of the sheath comprising the attenuating member. At step 1160, the emitters on the laser catheter are activated, thereby initiating the formation of laser-induced pressure waves a portion of which at least pass through the sheath, including the attenuating member, thereby disrupting the calcium in the vasculature. That is, the laser-induced pressure waves crack the calcified portion(s) and/or break the calcified portions of the tissue (e.g., media) and/or tissue layers (e.g., media layer) into smaller particles. Disrupting the calcified portion(s) within the tissue(s) of the blood vessel cracks the calcified portion(s) because the laser-induced pressure waves are absorbed by the calcified portions, thereby increasing the arterial wall's compliance, which in turn leads to improved blood flow and positive implications for other health conditions.
Step 1170 of method 1100 may include continuing to insert liquid medium to the distal end of the laser catheter and axially translate the laser catheter and/or the sheath to disrupt a portion of the calcified tissues of the blood vessel in the same portion or other portions of the vasculature. And any of the steps of method 1100 may be repeated until a sufficient amount of calcium is disrupted and the arterial wall's compliance is satisfactorily increased, as set forth in step 1180.
Additionally, although it is not disclosed in
Referring to
Referring to
The attenuating member may include a coil or coils 1268 integrally formed from flat wire within the sheath 1212. An example of the flat wire is shown in
As discussed herein, it may be desirable for the ratio of the open area for the attenuating member in comparison to the overall area of the attenuating member to be within a certain range, such as between 30 percent to 70 percent, and possibly between 40 percent and 60 percent, and more possibly between 45 percent and 55 percent, such as 45, 46, 47, 48, 49, 50, 51, 52, 53, 54 or 55 percent. Although round wire may be used to create the coil(s) 1268, using flat wire to construct the coil(s) 1268 may provide the attenuating member with an overall thinner longitudinal cross-sectional profile while decreasing the amount of open area per wrap of the wire because the height of the flat wire may be smaller than the width of the flat wire. The width of the flat wire provides the desired ratio of open area for the attenuating member in comparison to the overall area of the attenuating member, while the height of the material increases the coil(s) strength to withstand the laser-induced pressure wave without breaking. In other words, a smaller longitudinal cross-sectional profile reduces the overall diameter of the sheath assembly, thereby allowing the kit to enter smaller sized vasculature, while maintaining sufficient strength and rigidity to absorb and attenuate the laser-induced pressure wave.
There are three factors in determining the percentage of open area in the attenuating member: (1) the width of the flat wire (or diameter of the round wire); (2) the number of wraps of the wire; and (3) the gap between each wrap of wire. Once two of these factors are determined for a desired percentage of open area in the attenuating member, the third factor can be solved. In order to maintain a certain percentage of open area in the attenuating member, there is an inverse relationship between the number of wraps and the width of the flat wire (or diameter of the round wire). That is, for a certain percentage of open area in the attenuating member, the necessary wraps per inch decreases with a wire having a larger width, and the necessary wraps per inch increases with a wire having a smaller width. Additionally, there is also an inverse relationship between the number of wraps per inch and the gap between the wire wraps. That is, for a certain percentage of open area in the attenuating member using a predetermined wire size, the wraps per inch increases with a smaller gap between the wire(s). Moreover, there is a direct relationship between the size of the gap between the wire and the amount of open area in the attenuating member. That is, for a given wire width, the greater the gap between each winding, the larger the open area in the attenuating member, and the smaller the gap between each winding, the smaller the open area in the attenuating member.
For example, assuming that the attenuating member is constructed of 0.005 inch wide by 0.001 tall inch flat wire with a desired open area between 30 percent and 70 percent, the attenuating member may include between about 75 and 125 wraps (or revolutions) per inch. Specifically, a gap of about 0.008 inches between each wrap of 0.005 inch wide flat wire produces an open area of about 61.5 percent, and a gap of about 0.003 inches between each wrap of 0.005 inch wide flat wire produces an open area of about 37.5 percent. Additionally, a gap of about 0.005 inches between each wrap of 0.005 inch wide flat wire produces an open area of about 50 percent. The attenuating member, therefore, may be constructed from the flat wire such that the attenuating member includes between 75 and 125 wraps (or revolutions) per inch of the flat wire, between 80 and 120 wraps per inch of the flat wire, between 85 and 115 wraps per inch of the flat wire, between 90 and 110 wraps per inch of the flat wire depending upon the amount of open area within the attenuating member, the size (i.e., width) of the wire and the gap between each wrap of the wire. As such, it may also be preferable for the attenuating member to include about 75, 80, 85, 90, 95, 100, 105, 110, 115, 120 or 125 wraps per inch of the flat wire, wherein the flat wire is wound such that the width (X) of the flat wire is parallel with the longitudinal axis of the sheath 1212, and the height (Y) of the flat wire is perpendicular with the longitudinal axis of the sheath 1212. Additionally, if it desirable for the attenuating member to have a desired open area between 30 percent and 70 percent using a 0.004 inch wide flat wire, the gap between windings may be between, 0.0017 and 0.0093 inches respectively. These are examples, which shall not limit the scope of this disclosure because it may be desirable to have a flat wire with dimensions of 0.0002 to 0.010 inches wide and 0.0005 to 0.002 inches high, as well as round wire having a diameter between 0.0005 to 0.010 inches. For these ranges of wire size, the gap between the wire winding(s) and the wraps per length (inch) can be adjusted accordingly to produce the desired open area in the attenuating member.
Upon forming the sheath 1212 with the internally disposed attenuating member, the sheath 1212 may have an inner diameter between 0.010 and 0.200 inches and an outer diameter of about 0.014 inches such that the wall thickness of the sheath 1212 is between 0.002 and 0.015 inches. The sheath 1212 may be constructed of a polymeric material, such as Nylon-12. As mentioned above, distal end portion 1240 may also include an inner liner 1296 radially or concentrically disposed within the sheath 1212. The inner liner 1296 may be constructed of a polymer such as a polyimide having a thickness between 0.0005 and 0.010 inches, such as 0.0005, 0.0006, 0.0007, 0.0008, 0.0009, 0.001, 0.0015, 0.002, 0.00025, 0.003, 0.0035, 0.004, 0.0045, 0.005, 0.0055, 0.006, 0.0065, 0.007, 0.0075, 0.008, 0.0085, 0.0090, 0.0095 and 0.010 inches.
Again, the distal end portion 1240 of the sheath assembly 1204 may comprise an outer band 1272, which may also be referred to as a marker band, disposed about the distal end of the sheath 1212 and a tapered tip 1276 disposed distally of the outer band 1272. The outer band 1272 may be constructed of a highly radiopaque material, such as platinum iridium alloy or polymers doped with radiopaque materials such as barium sulfate, bismuth subcarbonate, bismuth trioxide, or tungsten. The tapered tip 1276 may be constructed of the same material as the sheath 1212 or an alternative material, such as nylon, pebax, polysulfone, HDPE, LDPE, UHMWPE, polypropylene, polyolefins, carbothane, polyurethane, Suralyn, ionomers, Estane, EPTFE, PTFE, or FEP. The tapered tip 1276 may, therefore, be formed integrally with the sheath 3012 or as a separate component. The circumference of the tapered tip 1276 may taper radially inward from its proximal end to its distal end between 1 degree and 10 degrees, such as 1, 2, 3, 4, 5, 6, 7, 8, 9 or 10 degrees.
It may also be preferable for the inner diameter of the tapered tip 1276 to be slightly less than the inner diameter of the inner liner 1296 of the sheath 1212, particularly if the inner liner 1296 is omitted from the distal end 1240 of the sheath assembly 1204. For example, it may be preferable for the tapered tip 1276 to seal the interface between the sheath assembly 1204 and the laser catheter assembly 1208 such that the escape of the liquid medium at the distal end of the kit 1200 is minimized or reduced. If a 5 French sized laser catheter 1280 of the laser catheter assembly 1208 has an outer diameter of about 0.056 inches, then it may be preferable for the inner diameter of the tapered tip 1276 to be about 0.057 inches, thereby leaving a radial distance or gap of about 0.0005 inches between the laser catheter 1280 and the tapered tip 1276. For the purposes of this disclosure about 0.0005 inches means 0.0001 to 0.001 inches. Additionally, if a 6 French sized laser catheter 1280 of the laser catheter assembly 1208 has an outer diameter of about 0.069 inches, then it may be preferable for the inner diameter of the tapered tip 1276 to be about 0.070 inches, thereby leaving a distance or gap of about 0.0005 inches between the laser catheter 1280 and the tapered tip 1276. Although the embodiments described above includes a gap of about 0.0005 inches between the laser catheter 1280 and the tapered tip 1276, such gap may be between 0 and 0.002 inches and still perform a sufficient seal.
The gap between the laser catheter 1280 and the inner liner 1296 (of the sheath 1212) will preferably be greater than the gap between the laser catheter 1280 and tapered tip 1276, thereby allowing the liquid medium to enter such gap between the laser catheter 1280 and the inner liner 1296. For example, for a 5 French sized laser catheter 1280 of the laser catheter assembly 1208 having an outer diameter of about 0.056 inches, it may be preferable for the inner diameter of the inner liner 1296 to be about 0.0615 inches, thereby leaving a radial distance or gap of about 0.00275 inches between the laser catheter 1280 and the inner liner 1296, which is about five times the gap between the gap between the laser catheter 1280 and the tapered tip 1276. For a 6 French sized laser catheter 1280 of the laser catheter assembly 1208 having an outer diameter of about 0.069 inches, it may be preferable for the inner diameter of the inner liner 1296 to be about 0.0745 inches, thereby leaving a distance or gap of about 0.00275 inches between the laser catheter 1280 and the inner liner 1296, which is about five times the gap between the gap between the laser catheter 1280 and the tapered tip 1276. Accordingly, the diameter of the lumen in the inner liner 1296 is greater than the diameter of the lumen in the tapered tip 1276. Although the embodiments described above includes a radial gap of about 0.00275 inches between the laser catheter 1280 and the inner liner 1296, such radial gap may be between about 0.001 and 0.010 inches and still provide a sufficient amount of liquid medium to enter the radial gap and create the desired pressure wave upon exposure to the laser light energy.
Referring to
Referring to
Once the laser catheter assembly 1208 and the sheath assembly 1204, particularly the laser catheter 1280 and the sheath 1212, respectively, are located within the patient's vasculature, the laser catheter 1280 is positioned beyond the distal end of the sheath 1212 and adjacent the vascular occlusion at step 1520. The clinician using the kit 1200 will be able to determine that the laser catheter assembly 1208, particularly the emitters 1288 is positioned beyond the distal end 1240 of the sheath assembly 1204 and adjacent the vascular occlusion because the radiopaque outer band 1284 of the laser catheter 1280 will be illustrated under fluoroscopy as being distal of the outer band 1272 of the sheath assembly 1204, as illustrated in
After the vascular occlusion (or a portion thereof) is removed from the vasculature, step 1530 may then be performed. Step 1530 includes positioning the sheath assembly 1204 over the laser catheter assembly 1208, particularly the sheath 1212 over the laser catheter 1280, within vasculature of a subject and adjacent the vascular occlusion similar to the way in which the sheath 250 and the catheter 170 are situated in
Once the distal portions 1240, 1260 of the sheath assembly 1204 and laser catheter assembly 1208 are disposed adjacent the vascular occlusion, such that the emitters 1288 and the attenuating member 1268 are axially aligned adjacent the vascular occlusion, the liquid medium may be introduced to the distal end 1260 of the laser catheter assembly 1208 as set forth in step 1535 of
During disruption of the calcium, it may be desirable to adjust the settings of the laser system to which the laser catheter assembly 1208 is coupled such that the emitters 1288 produce a fluence between 30 and 80 mJ/mm2, more preferably between 40 and 70 mJ/mm2, and even more preferably at a fluence of 45, 50, 55, 60 mJ/mm2. It may also be desirable for the repetition rate of the laser to be between 25 hertz and 80 hertz, including 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75 and 80 hertz. It may also be desirable for the pulse width of the laser to be between 125 nanoseconds and 200 nanoseconds, including 125, 130, 135, 140, 145, 150, 155, 160, 165, 170, 175, 180, 185, 190, 195 and 200 nanoseconds. As also discussed herein, the wavelength of the laser light energy and that emitted by the emitters may include a variety of wavelengths, including a wavelength of between about 150 nanometers to about 400 nanometers such as 308 nanometers.
If the laser catheter assembly 1208 and the sheath assembly 1204 are continued to be used to disrupt a portion of the vascular occlusion, then laser catheter assembly 1208 and sheath assembly 1204 are used as set forth in step 1540. If, however, the clinician wishes to discontinue using the laser catheter assembly 1208 and the sheath assembly 1204 to disrupt a portion of the vascular occlusion and use the laser catheter assembly 1208 to perform additional ablation, then the clinician repeats step 1520 (as well as the additional subsequent steps), as depicted in
As discussed above, transmitting pulses of light energy from an emitter into a liquid medium creates laser-induced pressure waves and/or vapor bubbles and additional resultant pressure waves that disrupt at least a portion of a vascular occlusion. The catheter may include a guidewire lumen through which a guidewire can pass and cross the vascular occlusion. It may also be desirable to excite and vibrate the guidewire to increase the guidewire's ability to pierce and cross the vascular occlusion. Accordingly, the present disclosure also contemplates directing the laser light energy emitted by the emitter into the liquid medium in a direction which causes the liquid medium to propagate laser-induced pressure waves toward the guidewire lumen and/or guidewire such that the laser-induced pressure waves excite and vibrate the guidewire.
Although the method illustrated in
Similar to how the laser catheter assembly 1208 and the sheath assembly 1204 of
Referring to
Referring now to
The tapered tip 1776 may be constructed of various materials, such as nylon, pebax, polysulfone, high-density polyethylene (HDPE), low-density polyethylene (LDPE), ultra-high-molecular-weight polyethylene (UHMWPE), polypropylene, polyolefins, carbothane, polyurethane, Suralyn, ionomers, Estane, expanded polytetrafluoroethylene (EPTFE), polytetrafluoroethylene (PTFE), or fluorinated ethylene propylene (FEP). The tapered tip 1776 may be formed integrally with the sheath 1712 or as a separate component. The circumference of the tapered tip 1776 may taper radially inward from its proximal end to its distal end between 1 degree and 10 degrees, such as 1, 2, 3, 4, 5, 6, 7, 8, 9 or 10 degrees. It may be preferable for the tapered tip 1776 to have an inner diameter that facilitates sealing the interface between the sheath assembly 1704 and the laser catheter assembly such that the escape of the liquid medium at the distal end of the kit is minimized or reduced. If a 6 French sized laser catheter of the laser catheter assembly has an outer diameter of about 0.069 inches, then it may be preferable for the inner diameter of the tapered tip 1776 to be about 0.058 inches. If a 7 French sized laser catheter of the laser catheter assembly is to be used, it may be preferable for the inner diameter of the tapered tip 1776 to be about 0.071 inches. If an 8 French sized laser catheter of the laser catheter assembly is to be used, it may be preferable for the inner diameter of the tapered tip 1776 to be about 0.082 inches.
The outer band 1772, which may also be referred to as a marker band, may be constructed of a highly radiopaque material, such as platinum iridium alloy or polymers doped with radiopaque materials such as barium sulfate, bismuth subcarbonate, bismuth trioxide, or tungsten.
Referring specifically to
The outer jacket 1778 may be constructed of various materials, such as nylon, pebax, polysulfone, HDPE, LDPE, UHMWPE, polypropylene, polyolefins, carbothane, polyurethane, Suralyn, ionomers, Estane, EPTFE, PTFE, or FEP. If a 6 French sized laser catheter of the laser catheter assembly is to be used, the outer jacket 1778 may provide the sheath 1712 with an outer diameter between 0.058 and 0.098 inches, such as 0.058, 0.062, 0.066, 0.070, 0.074. 0.078, 0.082, 0.086, 0.090, 0.094, and 0.098 inches. If a 7 French sized laser catheter of the laser catheter assembly is to be used, the outer jacket 1778 may provide the sheath 1712 with an outer diameter between 0.071 and 0.111 inches, such as 0.071, 0.075, 0.079, 0.083, 0.087, 0.091, 0.095, 0.099, 0.103, 0.107, and 0.111 inches. If an 8 French sized laser catheter of the laser catheter assembly is to be used, the outer jacket 1778 may provide the sheath 1712 with an outer diameter between 0.082 and 0.122 inches, such as 0.082, 0.086, 0.090, 0.094, 0.098, 0.102, 0.106, 0.110, 0.114, 0.118, and 0.122 inches. The outer jacket 1778 may have a wall thickness between 0.0015 and 0.0035 inches, such as 0.0015, 0.0017, 0.0019, 0.0021, 0.0023, 0.0025, 0.0027, 0.0029, 0.0031, 0.0033, and 0.0035.
The attenuating member 1768 is a braided structure 1768. The braided structure 1768 may include between 4 and 28 carriers and more particularly between 12 and 20 carriers, such as 12, 13, 14, 15, 16, 17, 18, 19, or 20 carriers. Each carrier may include between 1 and 10 wires, such as 1, 2, 3, 4, 5, 6, 7, 8, 9, and 10 wires. Each wire may have a cross-sectional height between 0.0005 and 0.005, such as 0.0005, 0.0007, 0.0009, 0.001, 0.002, 0.003, 0.004, and 0.005. Each wire may be a flat wire having a cross-sectional width between 0.0005 and 0.003, such as 0.0005, 0.0007, 0.0009, 0.001, 0.002, and 0.003. Each wire may be constructed of stainless steel, such as 304 stainless steel, or other type of metal or metal alloy. The braided structure 1768 may have a braid density between 20 and 100 picks per inch (PPI) and particularly between 40 and 80 PPI, such as 40, 44, 48, 52, 56, 60, 64, 68, 72, 76, and 80 PPI. The relationship between the open area and the closed area (or the ratio of the open area to the overall area) within the braided structure 1768 should be such that a sufficient amount of laser-induced pressure waves pass through the braided structure 1768, and the open area should allow the laser-induced pressure waves to pass therethrough, while also limiting the size of the vapor bubbles that can form on the exterior of the sheath 1712. The braided structure 1768 may have an open area between 45 percent and 85 percent, and possibly between 55 percent and 75 percent, such as 55, 56, 57, 58, 59, 60, 61, 62, 63, 64, 65, 66, 67, 68, 69, 70, 71, 72, 73, 74, or 75 percent. The open area of the braided structure depends on the braid density, the number of carriers in the braided structure 1768, the number of wires in each carrier, and the dimensions of the wires.
The intermediate layer 1770 may be constructed of various materials, such as nylon, pebax, polysulfone, HDPE, LDPE, UHMWPE, polypropylene, polyolefins, carbothane, polyurethane, Suralyn, ionomers, Estane, EPTFE, PTFE, or FEP. The intermediate layer 1770 may have a wall thickness between 0.0005 and 0.0025 inches, such as 0.0005, 0.0007, 0.0009, 0.0011, 0.0013, 0.0015, 0.0017, 0.0019, 0.0021, 0.0023, and 0.0025.
The inner liner 1775 may be constructed of various materials, such as a polyamide or a fluoropolymer, specifically Neoflon FEP NP-101 available from Daikin America. If a 6 French sized laser catheter of the laser catheter assembly is to be used, the inner liner 1775 may provide the sheath 1712 with an inner diameter between 0.040 and 0.080 inches, such as 0.044, 0.048, 0.052, 0.056, 0.060, 0.064, 0.068, 0.072, 0.076 and 0.080 inches. If a 7 French sized laser catheter of the laser catheter assembly is to be used, the inner liner 1775 may provide the sheath 1712 with an inner diameter between 0.053 and 0.093 inches, such as 0.053, 0.057, 0.061, 0.065, 0.069, 0.073, 0.077, 0.081, 0.085, 0.089, and 0.093 inches. If an 8 French sized laser catheter of the laser catheter assembly is to be used, the inner liner 1775 may provide the sheath 1712 with an inner diameter between 0.064 and 0.104 inches, such as 0.064, 0.068, 0.072, 0.076, 0.080, 0.084, 0.088, 0.092, 0.096, 0.100, and 0.104 inches. The inner liner 1796 may have a wall thickness between 0.0005 and 0.0025 inches, such as 0.0005, 0.0007, 0.0009, 0.0011, 0.0013, 0.0015, 0.0017, 0.0019, 0.0021, 0.0023, and 0.0025.
Kits including the sheath assembly 1704 can be used to perform any of the methods described herein. In some embodiments, the sheath assembly 1704 is capable of resisting damage for a duration of at least 1, 2, 3, 4 or 5 minutes (or any duration therebetween) when laser pulses are emitted by a laser catheter during performance of such methods. More specifically, the sheath 1704 is capable of resisting damage when using Spectranetics 1.4, 1.7, and 2.0 Turbo-Elite™ and 2.0 Turbo-Power™ laser catheters to emit laser pulses at 60 fluence and 25 Hz into a contrast medium of fifty percent (50%) Optiray 320 contrast with saline, infused to the sheath 1704 at 5 mL/min. To facilitate this capability, one or both of the outer jacket 1778 and the intermediate layer 1770 may be integrally formed with the braided structure 1768 (that is, formed in manner that causes one or both of the outer jacket 1778 and the intermediate layer 1770 to occupy at least some of the open area of the braided structure). For example, the inner liner 1775 may be extruded, the intermediate layer 1770 may be over-extruded on the inner liner 1775, the braided structure 1768 may be positioned over the intermediate layer 1770, and the outer jacket 1778 may be over-extruded on the braided structure 1768. The sheath 1712 is laminated, coupled to the Luer fitting 1720, and the outer jacket 1778 may be stripped at the distal end of the sheath 1712.
In comparison to conventional unreinforced and/or reinforced sheaths, such as in comparison to sheath assemblies that include various or multiple laminated layers or sheath assemblies using other manufacturing processes, the sheath assembly 1704 disclosed and discussed herein with respect to
Referring to
As discussed above herein, smaller-sized blood vessels require a laser catheter having a reduced diameter for vessel entry, and the smaller-sized laser catheters may have limitations as to the amount of energy that can transfer. That is, the reduced sized laser catheters may have less optical fibers or smaller diameter optical fibers in comparison to larger sized laser catheters, thereby limiting the amount of energy that the reduced sized laser catheters can transfer before causing damage to the optical fibers. And if the optical fibers attempt to transfer too much energy, they will be damaged.
The amount of energy transmitted by the laser-induced pressure waves to the blood vessel (and the calcium included therein) is proportional to the amount of energy transmitted by the optical fibers to the liquid medium within the outer sheath. That is, the more energy transmitted by the optical fibers to the liquid medium, the greater the amount of energy transmitted by the laser-induced pressure waves to the blood vessel will be. Also, the less energy transmitted by the optical fibers to the liquid medium, the lesser the amount of energy transmitted by the laser-induced pressure waves to the blood vessel will be. Because smaller sized laser catheters may have less optical fibers or smaller diameter optical fibers, the amount of energy transferred by the optical fibers to the liquid medium, the amount of energy transmitted by the laser-induced pressure waves to the blood vessel is limited, thereby potentially limiting the ability to disrupt calcium in the blood vessel.
One way to compensate for the reduction in energy transferred through and emitted by the laser catheter includes increasing the amount of contrast in the liquid medium within the outers sheath. Transmitting pulses of light energy into the liquid medium produces vapor bubbles. Upon emitting light from an emitter, such as a laser catheter, within a sheath that contains an absorptive liquid medium, vapor bubbles may be produced within the interior of the sheath and/or exterior to the sheath. But increasing the amount of contrast may create an undesirably sized vapor bubble, either within or on the outside of the sheath, thereby potentially damaging the blood vessel.
Again, the outer sheath 1912 depicted in
Continuing to refer to
Although the intermediate layers 1970 and attenuating members 1968 in
Regarding the overall size of the outer sheath 1912, it may be desirable to use a 4 French, 5 French, 6 French, 7 French or 8 French sized catheter in the vasculature below the knee of the patient. In general, it is desirable for the alternating attenuating members 1968 to have a relatively higher density in comparison to the intermediate layers 1970, which will have a lower density in comparison to the attenuating members 1968. With respect to materials for catheters, such as polymers, elastomers, rubbers and plastics, density may be correlated to hardness. For the purposes of this disclosure, assuming that the intermediate layer and the attenuating member made of different types of these materials and the intermediate layer and the attenuating member are solid, the higher the density that the material is, the higher the hardness will likely be, and the lower the density that the material is, the lower the hardness will likely be. In other words, density and hardness for catheter materials are directly related—as one increases so does the other, and as one decreases so does the other. So, it is desirable to alternate a harder layer (e.g., the attenuating members 1968) with a relatively softer layer (e.g., intermediate layers 1970). Notwithstanding the foregoing, for the purposes of this disclosure, it shall be understood that if an attenuating member 1968 is constructed of metal and the intermediate layer 1970 is constructed of a polymer, elastomer, rubber or plastic, then the attenuating member 1968 shall be considered to have a greater density than the intermediate layer 1970, even if the attenuating member 1968 has openings, is porous or is coiled, such as the configurations illustrated in
Hardness may be tested using a durometer, which is a type of gauge to measure the resistance to surface penetration. There are several scales of durometer, used for materials with different properties. The two common scales, using slightly different measurement systems, are the ASTM D2240 type A and type D scales. The A scale is for softer ones, while the D scale is for harder ones. Higher numbers on the scales indicate a greater resistance to indentation and thus harder materials. Lower numbers indicate softer, more flexible materials, while higher numbers indicate harder and typically more durable materials.
Along with the number there is usually an alpha scale rating with “A” being softer materials and “D” for harder materials. This is scale is typically used for rubbers/elastomers and softer plastics such as polyolefins, fluoropolymers, and vinyls. The hardness value is determined by the penetration of the durometer indenter foot into the sample. Shore A is usually used for flexible materials and Shore D is used for semi-flexible materials.
Although Shore A is one scale, and Shore D is another scale, there may be overlap between these two scales. For example, the Shore A scale may have a hardness of 0 to 100, and the Shore D scale may have a hardness of 0 to 100, but a range of Shore 60A to Shore 100A may overlap with a range of Shore OD to Shore 60D. That is, a hardness range of Shore 40A overlaps with a hardness range of Shore 60D.
Another hardness scale is the Rockwell scale. Rockwell hardness is generally chosen for ‘harder’ plastics such as nylon, polycarbonate, polystyrene, and acetal. Three common Rockwell scales are Rockwell A, Rockwell B, and Rockwell C. As with the Shore scale, a higher number indicates a harder material.
Although the Shore scale(s) is one scale, and the Rockwell scale(s) is another scale, there may be overlap between these two scales. For example, the Shore D scale may have a hardness of 0 to 100, and the Rockwell B scale may have a hardness of 0 to 110, but a range of Shore 75D to Shore 100D may overlap with a range of Rockwell OB to Rockwell 40B. That is, a hardness range of Shore 25D overlaps with a hardness range of Rockwell 40B. However, due to differences in methods of measurement, it may not be possible to directly interconvert between the scales.
If an outer jacket 1978 is included in the construction of the outer sheath 1912, it may be desirable for the durometer and/or density of the outer jacket 1978 to be the same or relatively similar to the durometer and/or density of the intermediate layer 1970 or it may be desirable for the durometer and/or density of the outer jacket 1978 to be between the durometers and/or densities of the attenuating members 1968 and intermediate layers 1970. That is, it is desirable for the durometer and/or density of the outer jacket 1978 to be less than the durometer and/or densities of the attenuating members 1968, and the durometer and/or density of the outer jacket 1978 may be the same or greater than the durometer and/or density of the intermediate layers 1970.
As mentioned above, one of the keys to increasing the amplitude of the pressure waves that transmit through the sheath and minimizing the size of the undesirable vapor bubble is to increase the number of layers of pairs of alternating attenuating members 1968 and intermediate layers 1970 creates a composite structure that mimics anisotropic metamaterial. And the alternating durometers of the plurality of attenuating members 1968 and intermediate layers 1970 creates this composite structure that amplifies the pressure waves.
For example, it may be desirable for the differences in durometer (or hardness) between the attenuating members 1968 and the intermediate layers 1970 to be a difference of about Shore 5A, Shore 10A, Shore 15A, Shore 20A, Shore 25A, Shore 30A, Shore 35A, Shore 40A, Shore 45A, Shore 50A, Shore 55A, Shore 60A, Shore 65A or Shore 70A. It may be also desirable for the differences in durometer (or hardness) between the attenuating members 1968 and the intermediate layers 1970 to be a difference of about Shore 5D, Shore 10D, Shore 15D, Shore 20D, Shore 25D, Shore 30D, Shore 35D, Shore 40D, Shore 45D, Shore 50D, Shore 55D, Shore 60D, Shore 65D or Shore 70D. It may also be desirable for the differences in durometer (or hardness) between the attenuating members 1968 and the intermediate layers 1970 to be a difference of about Rockwell 5B, Rockwell 10B, Rockwell 15B, Rockwell 20B, Rockwell 25B, Rockwell 30B, Rockwell 35B or Rockwell 40B.
Because the attenuating member 1968 may be constructed of a material the hardness of which may be better suited to be determined using one scale, and the intermediate layer 1970 may be constructed of a different material the hardness of which may be better suited to be determined using a different scale, then the hardness difference between materials may be determined using two or more scales. For example, if the attenuating member 1968 has a hardness of Shore 80D and the intermediate layer has a hardness of Shore 85A, which is similar to Shore 35D, then the difference in hardness is about Shore 45D. Additionally, if the attenuating member 1968 has a hardness of Shore 90D and the intermediate layer has a hardness of Shore 40A, and there is no overlap between the Shore A scale (which has a range of 0-100) at the relevant hardness and the Shore D scale, then the difference in hardness is Shore 60A plus Shore 30D (which has range of 0-100 and Shore 100A overlaps at Shore 60D).
The attenuating member 1968 may be between Shore hardness 80D and Rockwell 80B, and potentially more desirable to be between Rockwell 20B and Rockwell 70B. It may be desirable for the durometer of the intermediate layers 1970 to be between Shore 20D and Shore 80D, and potentially more desirable to be between Shore hardness 35D and Shore 75D. It may be desirable for the durometer of the outer jacket 1978 to be similar to the intermediate layer 1970.
The densities of the attenuating member 1968 and the intermediate layer 1970 may be different solely due to the differences in materials while the thicknesses for the attenuating member 1968 and the intermediate layer 1970 are substantially the same. Additionally or alternatively, the densities of the attenuating member 1968 and the intermediate layer 1970 may be different due to the differences in both the materials and thicknesses for the attenuating member 1968 and the intermediate layer 1970.
Referring again to
The attenuating members 1968 may be a solid or porous structure such as those described in this disclosure, including those constructed of various metallic and polymeric materials. If the attenuating members 1968 are porous, they may be a braided or coiled structure. If the attenuating members 1968 are braided, the braided structure may include between 4 and 28 carriers and more particularly between 12 and 20 carriers, such as 12, 13, 14, 15, 16, 17, 18, 19, or 20 carriers. Each carrier may include between 1 and 10 wires, such as 1, 2, 3, 4, 5, 6, 7, 8, 9, and 10 wires. Each wire may have a cross-sectional height between 0.0002 and 0.005 inches, such as 0.0002, 0.0003, 0.0005, 0.0007, 0.0009, 0.001, 0.002, 0.003, 0.004, and 0.005 inches. Each wire may be a flat wire having a cross-sectional width between 0.0002 and 0.003 inches, such as 0.0002, 0.0003, 0.0005, 0.0007, 0.0009, 0.001, 0.002, and 0.003 inches. Each wire may be constructed of stainless steel, such as 304 stainless steel, or other type of metal or metal alloy. The braided structure may have a braid density between 20 and 200 picks per inch (PPI) and particularly between 40 and 80 PPI, such as 40, 44, 48, 52, 56, 60, 64, 68, 72, 76, and 80 PPI. The relationship between the open area and the closed area (or the ratio of the open area to the overall area) within the braided structure 1968 should be such that a sufficient amount of laser-induced pressure waves pass through the braided structure 1968, and the open area should allow the laser-induced pressure waves to pass therethrough, while also limiting the size of the vapor bubbles that can form on the exterior of the sheath 1912. The braided structure 1968 may have an open area between 45 percent and 85 percent, and possibly between 55 percent and 75 percent, such as 55, 56, 57, 58, 59, 60, 61, 62, 63, 64, 65, 66, 67, 68, 69, 70, 71, 72, 73, 74, or 75 percent. The open area of the braided structure depends on the braid density, the number of carriers in the braided structure, the number of wires in each carrier, and the dimensions of the wires.
The thickness of the attenuating members 1968 may be between 0.0002 and 0.0030 inches, such as 0.0002, 0.0005, 0.00075, 0.0010, 0.0015, 0.0020, 0.0025, and 0.0030 inches. Each attenuating member 1968 in the outer sheath 1912 may have the same (or similar) or different thickness and porosity. For example, each attenuating member 1968 in the outer sheath 1912 may increase in size or decrease in size as the attenuating members progress from the inner liner 1996 to the outer jacket 1978.
Similar to the attenuating members 1968, the intermediate layers 1970 may have the same (or similar) or different thickness. For example, each intermediate layer 1970 may increase or decrease proportionately to the adjustment in thickness of the attenuating member 1968 in the outer sheath 1912 as the attenuating members progress from the inner liner 1996 to the outer jacket 1978. Or each intermediate layer 1970 may increase or decrease inversely in thickness to the adjustment in thickness of the attenuating member 1968 in the outer sheath 1912 as the attenuating members progress from the inner liner 1996 to the outer jacket 1978.
The intermediate layers 1970 may be constructed of various materials, such as nylon, pebax, polysulfone, HDPE, LDPE, UHMWPE, polypropylene, polyolefins, carbothane, polyurethane, Suralyn, ionomers, Estane, EPTFE, PTFE, or FEP. The intermediate layers 1970 may have a wall thickness between 0.0002 and 0.0030 inches, such as 0.0002, 0.0005, 0.00075, 0.0010, 0.0015, 0.0020, 0.0025, and 0.0030 inches.
The inner liner 1996 may be constructed of various materials, such as a polyamide or a fluoropolymer, specifically Neoflon FEP NP-101 available from Daikin America, PTFE, FEP, PFA, ETFE, EFEP. If a 6 French sized laser catheter of the laser catheter assembly is to be used, the inner liner 1996 may provide the sheath 1912 with an inner diameter between 0.040 and 0.080 inches, such as 0.044, 0.048, 0.052, 0.056, 0.060, 0.064, 0.068, 0.072, 0.076 and 0.080 inches. If a 7 French sized laser catheter of the laser catheter assembly is to be used, the inner liner 1996 may provide the sheath 1912 with an inner diameter between 0.053 and 0.093 inches, such as 0.053, 0.057, 0.061, 0.065, 0.069, 0.073, 0.077, 0.081, 0.085, 0.089, and 0.093 inches. If an 8 French sized laser catheter of the laser catheter assembly is to be used, the inner liner 1996 may provide the sheath 1912 with an inner diameter between 0.064 and 0.104 inches, such as 0.064, 0.068, 0.072, 0.076, 0.080, 0.084, 0.088, 0.092, 0.096, 0.100, and 0.104 inches. The inner liner 1996 may have a wall thickness between 0.0002 and 0.0025 inches, such as 0.0005, 0.0007, 0.0009, 0.0011, 0.0013, 0.0015, 0.0017, 0.0019, 0.0021, 0.0023, and 0.0025.
Although
The outer sheath 1912 depicted in
Replacing the sheaths discussed elsewhere in this disclosure with the outer sheath 1912 depicted in
Although a large portion of this disclosure includes a discussion of laser ablation catheters used in conjunction with a sheath assembly to perform CAD and PAD procedures, other the laser ablation catheter and sheath assembly may be used to perform other types of medical and/or surgical procedures. Laser catheters typically transmit laser energy through optical fibers housed in a relatively flexible tubular catheter inserted into a body lumen, such as a blood vessel, ureter, fallopian tube, cerebral artery and the like to remove obstructions or restrictions in the lumen. Catheters used for laser angioplasty and other procedures may have a central passageway or tube which receives a guide wire inserted into the body lumen (for example, vascular system) prior to catheter introduction. The guide wire facilitates the advancement and placement of the catheter to the selected portion(s) of the body lumen for laser ablation of tissue.
The present disclosure, in various aspects, embodiments, and configurations, includes components, methods, processes, systems and/or apparatus substantially as depicted and described herein, including various aspects, embodiments, configurations, sub combinations, and subsets thereof. Those of skill in the art will understand how to make and use the various aspects, aspects, embodiments, and configurations, after understanding the present disclosure. The present disclosure, in various aspects, embodiments, and configurations, includes providing devices and processes in the absence of items not depicted and/or described herein or in various aspects, embodiments, and configurations hereof, including in the absence of such items as may have been used in previous devices or processes, for example, for improving performance, achieving ease and\or reducing cost of implementation.
The foregoing discussion of the disclosure has been presented for purposes of illustration and description. The foregoing is not intended to limit the disclosure to the form or forms disclosed herein. In the foregoing Detailed Description for example, various features of the disclosure are grouped together in one or more, aspects, embodiments, and configurations for the purpose of streamlining the disclosure. The features of the aspects, embodiments, and configurations of the disclosure may be combined in alternate aspects, embodiments, and configurations other than those discussed above. This method of disclosure is not to be interpreted as reflecting an intention that the claimed disclosure requires more features than are expressly recited in each claim. Rather, as the following claims reflect, inventive aspects lie in less than all features of a single foregoing disclosed aspects, embodiments, and configurations. Thus, the following claims are hereby incorporated into this Detailed Description, with each claim standing on its own as a separate preferred embodiment of the disclosure.
Moreover, though the description of the disclosure has included description of one or more aspects, embodiments, or configurations and certain variations and modifications, other variations, combinations, and modifications are within the scope of the disclosure, for example, as may be within the skill and knowledge of those in the art, after understanding the present disclosure. It is intended to obtain rights which include alternative aspects, embodiments, and configurations to the extent permitted, including alternate, interchangeable and/or equivalent structures, functions, ranges or steps to those claimed, whether or not such alternate, interchangeable and/or equivalent structures, functions, ranges or steps are disclosed herein, and without intending to publicly dedicate any patentable subject matter.
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/EP2020/086059 | 12/15/2020 | WO |
| Number | Date | Country | |
|---|---|---|---|
| 62951331 | Dec 2019 | US |
