WO2010036560A1 - Endovascular sheath with gradable stiffness device and method - Google Patents
Endovascular sheath with gradable stiffness device and method Download PDFInfo
- Publication number
- WO2010036560A1 WO2010036560A1 PCT/US2009/057380 US2009057380W WO2010036560A1 WO 2010036560 A1 WO2010036560 A1 WO 2010036560A1 US 2009057380 W US2009057380 W US 2009057380W WO 2010036560 A1 WO2010036560 A1 WO 2010036560A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- sheath
- stiffening component
- actuating mechanism
- sheath apparatus
- inner tube
- Prior art date
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/0043—Catheters; Hollow probes characterised by structural features
- A61M25/005—Catheters; Hollow probes characterised by structural features with embedded materials for reinforcement, e.g. wires, coils, braids
- A61M25/0053—Catheters; Hollow probes characterised by structural features with embedded materials for reinforcement, e.g. wires, coils, braids having a variable stiffness along the longitudinal axis, e.g. by varying the pitch of the coil or braid
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/0043—Catheters; Hollow probes characterised by structural features
- A61M25/005—Catheters; Hollow probes characterised by structural features with embedded materials for reinforcement, e.g. wires, coils, braids
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/0043—Catheters; Hollow probes characterised by structural features
- A61M25/005—Catheters; Hollow probes characterised by structural features with embedded materials for reinforcement, e.g. wires, coils, braids
- A61M25/0051—Catheters; Hollow probes characterised by structural features with embedded materials for reinforcement, e.g. wires, coils, braids made from fenestrated or weakened tubing layer
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/0043—Catheters; Hollow probes characterised by structural features
- A61M25/0054—Catheters; Hollow probes characterised by structural features with regions for increasing flexibility
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/01—Introducing, guiding, advancing, emplacing or holding catheters
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/0043—Catheters; Hollow probes characterised by structural features
- A61M2025/0063—Catheters; Hollow probes characterised by structural features having means, e.g. stylets, mandrils, rods or wires to reinforce or adjust temporarily the stiffness, column strength or pushability of catheters which are already inserted into the human body
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/01—Introducing, guiding, advancing, emplacing or holding catheters
- A61M25/06—Body-piercing guide needles or the like
- A61M25/0662—Guide tubes
- A61M2025/0681—Systems with catheter and outer tubing, e.g. sheath, sleeve or guide tube
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/01—Introducing, guiding, advancing, emplacing or holding catheters
- A61M25/0102—Insertion or introduction using an inner stiffening member, e.g. stylet or push-rod
Definitions
- the invention relates to a sheath device with gradable stiffness and method that reduces or prevents buckling when inserted into a vascular tract.
- Endo vascular surgery has developed as a form of minimally invasive surgery that is used to access many regions of the body through major blood vessels.
- a catheter is introduced through the skin into a large blood vessel such as the femoral artery or vein.
- the catheter carries a radio-opaque dye that can be detected by X-ray or fluororscopic procedures.
- Endovascular surgery is becoming more widely used because it is minimally invasive and offers immediate advantages over more traditional, yet highly invasive surgeries.
- a catheter is a tube that can be inserted into a body cavity, duct or vessel.
- Catheters typically allow drainage or the injection of a fluid or access by surgical instruments.
- Many uses require that the catheter be thin and flexible (a "soft” catheter or tube); in other cases it may be a larger solid tube — a "hard” catheter.
- the term “sheath” refers to the outer covering of a guide wire. Unless the context dictates otherwise, it may be used interchangeably with the term “catheter,” and (2) the term “guide wire” refers to a long and flexible fine spring that is used to introduce and position an intravascular catheter. Conventionally, the catheter or sheath is often threaded over the wire — the wire may then be withdrawn, leaving the catheter in place, as taught by the Seldinger technique, a medical procedure that is used to obtain access to blood vessels and other hollow organs. Seldinger Sl (Catheter Replacement of the Needle in Percutaneous Arteriography; a New Technique). Acta Radiologica (5); 368-76 (1953).
- a catheter needs to be advanced through tortuous paths, in which it may be difficult to steer a guide wire or other interventional device along the interstices a vessel.
- one area in the vascular geometry that causes issues related to advancing a device is the interface of the femoral and aortic vessels.
- the entry location for devices is the femoral artery on the side of the body opposite the area of concern. The device must then pass over the femoral arch and into the opposite femoral artery.
- buckling of the device often occurs at the femoral/aortic interface.
- conventional interventional devices tend to buckle under the axial force reaction of the tortuous vessel to the pressures of insertion. Buckling of the device often occurs proximal to the tortuous anatomy.
- a guide wire must have some flexibility to be able to steer through the vascular anatomy without dissecting a vessel.
- a guide wire is typically a small diameter wire (.014") and is pliable and soft. When the guide wire is advanced through any tortuous anatomy, due to the small size of the wire, the wire has little ability to resist buckling. The proximal section of the wire typically buckles, and very little if any force is transmitted to the distal end of the wire.
- Guiding catheters and sheaths are conventionally made from reinforced extruded plastic tubing. These devices are soft and generally provide little resistance to buckling.
- the intervention devices that are used during the procedure.
- the intervention devices e.g. stent delivery systems and balloons
- the intervention devices are pliable along their axial shaft, and easily buckle when an axial force is applied.
- Most devices and techniques that are available do not provide a solution to the buckling that occurs when tortuous anatomy is encountered during a procedure. If a device can not be advanced through this tortuous anatomy, the procedure may not be able to be performed, and the outcome for the patient may be compromised.
- a sheath device with a simple design, that is easy to use in patients that require an interventional vascular procedure.
- a sheath device would be intuitive to use and require minimal surgical finesse, yet be able to negotiate a tortuous path that may include calcified lesions and fibrosed areas, swiftly and with repeatability if desired without disrupting adjacent tissue.
- the disclosed sheath device reduces the risk of vascular perforation by offering a tip design that does not ablate tissue ahead of its distal end, thereby avoiding inadvertent rupture of tissue that may be inadvertently contacted.
- the invention includes a device and method that reduces or prevents unwanted buckling of interventional devices.
- the inventive device allows the transmission of axial forces through the interventional devices to the distal end of the product without kinking or buckling. It would be desirable to have a differential level of stiffness along the length of a sheath. For example, the distal region of the sheath would desirably be fluffy or soft. This would reduce the risk of trauma that might otherwise be caused by interference between the distal end of the sheath and a tight turn in an arterial wall.
- one aspect of the invention includes a sheath that has a changing modulus of elasticity along its length.
- the sheath may have a modulus of elasticity along its length that could be discretely or gradually changed.
- Another facet of the invention is the provision of a sheath that has the capability to change its outside diameter along its length so that, for example, the outside diameter may be less at the distal than at the proximal end.
- These facets may also have applicability to designing a stent.
- an endovascular sheath apparatus comprising an inner tube which includes a lumen for introducing medical fluids or devices and an outer surface. Disposed outside the inner tube is an outer tube that has an interior surface. The respective outer and inner surfaces define a cavity therebetween. A stiffening component is at least partially received in at least part of the cavity. Cooperating with the stiffness component is an actuating mechanism.
- FIGURE 1 is an overall perspective, exploded view of several aspects of the invention (Embodiment #1);
- FIGURE 2 depicts a proximal position of a sliding mechanism (isometric view) when the device is in a "soft" position
- FIGURE 3 depicts a proximal position of a sliding mechanism with an outer tube (side elevation view);
- FIGURE 4 depicts a proximal position of the sliding mechanism with a helical tube stiffening component (side elevational view);
- FIGURE 5 depicts a distal portion of the sliding mechanism in a "stiff position (isometric view);
- FIGURE 6 depicts a proximal position of the sliding mechanism including the outer tube (side elevation view);
- FIGURE 7 depicts a proximal position of the sliding mechanism with the helical tube stiffening component, in which the outer tube is hidden and in which a helix is configured in a closed condition (side elevation view);
- FIGURE 8 depicts a slide mechanism that cooperates with locking detents for "soft” and “stiff” positions (sectioned, isometric view);
- FIGURE 9 depicts a sliding mechanism including an outer tube hub sliding track, in which a tracking tab is shown in a sliding position and a linear track is provided in an outer tube hub (sectioned, isometric view);
- FIGURE 10 depicts a braided wire or polymeric mesh in an open position (Embodiment #2);
- FIGURE 11 depicts the braided wire or polymeric mesh in a closed configuration
- FIGURE 12 depicts a proximal position of the sliding mechanism and outer tube (side elevational view);
- FIGURE 14 depicts a distal position of the sliding mechanism, in which the outer tube is shown (side elevation view);
- FIGURES 15 and 15A depict a proximal position of the sliding mechanism with the braided tube stiffening component, in which the outer tube is hidden (side elevation view);
- FIGURE 16 depicts an "open” position ("soft") of a rotational handle (Embodiment #3, side elevation view);
- FIGURE 17 depicts this embodiment with the rotational handle rotated to a "stiff position ("closed”; side elevation view);
- FIGURE 18 depicts an "open” position ("soft") of the helical rotation handle (Embodiment #4, side elevation view);
- FIGURE 19 depicts a helical rotation in which the handle has moved
- FIGURE 20 depicts a helical track in the outer tube hub (isometric view);
- FIGURE 21 depicts an optional safety mechanism that prevents accidental movement of the sliding mechanism (side elevation view);
- FIGURE 22 depicts the safety mechanism in a "locked" position
- FIGURE 23 depicts the safety mechanism in an "unlocked" position
- FIGURE 24 is a side elevational view of the embodiment of Figure 23;
- FIGURE 25 is a longitudinal sectional view of the embodiment of Figure 24 taken along the line XXV-XXV thereof;
- FIGURE 26 is a top view thereof
- FIGURE 27 is a sectional view of the embodiment of Figure 26 taken along the line XXVII-XXVII thereof;
- FIGURE 28 depicts additional sectional detail of a distal end region of the shaft.
- FIGURE 29 is an enlarged portion thereof.
- an endo vascular sheath apparatus 2 that has an inner tube 12 which includes a lumem 26 for introducing medical devices or fluids.
- the inner tube 12 has an outer surface 13 (best seen in Figures 28-29.)
- an outer tube 22 Positioned outside the inner tube 12 is an outer tube 22 that has an interior surface 23. Lying between the inner 23 and outer 13 surfaces is a cavity 28. At least a portion of the cavity 28 houses a stiffening component 20 that reinforces at least a portion of the inner tube 12 to minimize or prevent kinking.
- an actuating mechanism 18 In cooperation with the stiffening component 20, there is provided an actuating mechanism 18.
- the cavity 28 lies between the inner 12 and outer 22 tubes for placement of a tube stiffening component 20.
- proximal and distal describe the opposing axial ends of the endovascular sheath assembly 2 as well as the axial ends of a medical device with which the sheath is used, and its components.
- proximal refers to the end of the member (or component) that is closest to the surgeon during use.
- distal refers to the end of the member (or component) that is positioned closest to the end of the sheath assembly 2 that is initially inserted into the vascular system.
- the endovascular sheath 2 may include an inner tube hub 10 ( Figures 1-2), the proximal section of which it may if desired be attached to a valve system 6.
- the valve system 6 may serve as a one-way valve 14 by which fluid or device may be ducted into the inner tube 12.
- the one-way valve 6 may be incorporated into the inner tube hub 10.
- a hub section 10 optionally lies at an interface of the sheath assembly 2 with other interventional devices 4.
- the one-way valve 14 may optionally serve as a secondary piece.
- This valve prevents the flow of blood out of the device, but allows the introduction of interventional devices (guide catheters, wires, etc.) into the vasculature. It may also be a multiple piece design with a removable valve.
- the proximal section also optionally has a luer lock connection for flushing the device or injecting fluids into the system such as contrast-providing media.
- the outer tube 22 provides a smooth exterior surface to facilitate navigation along tortuous and possibly narrowing channels in the vascular system.
- a bond 15 ( Figure 28) may be provided at a distal region of the outer tube 22 in order to affix it to the inner tube 12.
- an outer tube hub 16 ( Figures 1-2) may be attached to the outer tube 22.
- the outer tube hub 16 attaches to the inner tube hub 10.
- the outer tube hub 16 provides a track 30 that guides in one embodiment the linear displacement of an actuating or sliding mechanism 18.
- the track 30 defines one or more locating features which in the embodiment depicted in Figure 8 include a detent 40 (distal, stiff) and a position 38 (proximal, soft).
- a tracking tab 42 is guided along the track 30 that is provided in the outer tube hub 16.
- the actuating mechanism 18 maybe positioned at an intermediate location if the surgeon desires the inner tube 12 to have a stiffness which is intermediate between that which results from positioning the actuating mechanism at locations 40 or 38.
- the actuating mechanism 18 communicates with a stiffening component 20 ( Figures 10-11) and interfaces with the outer tube hub 16 ( Figures 1-2).
- the stiffening component 20 has a distal end 8 that is affixed by bond 15 to the inner tube 12 at one end and to the actuating mechanism
- the inner tube 12 of the sheath assembly 2 conventionally includes a reinforced tubular section that is typically made of an extruded plastic. It is soft and pliable. The distal tip is preferably extremely soft to reduce the possibility of any vessel damage when the device 2 is introduced into an artery, such as the femoral artery.
- the body of the inner tubular section 12 is reinforced with the stiffening component 20, such as a braided material, preferably made of metal or strands of a plastic material. This helps prevent the tubular section 12 from susceptibility 60 being kinked, and gives a selective stiffening characteristic to the device 2 that resists buckling.
- One objective of the inventive design is to retain the functionality of the current products on the market, but give the interventionalist a sheath assembly 2 that has adjustable stiffness when required or desirable during the procedure.
- the inventive design incorporates variations in the stiffening component 20 of the sheath assembly 2. These variations help stiffen the body of the inner tubular section 12 of the sheath. This stiffening allows the interventionalist to more easily transmit axial force when desired to the distal end 8 of the device, thereby facilitating the passage of the device 2 through a tortuous anatomy.
- Embodiment #1 Helical Stiffening Component with Linear Slide
- the stiffening component 20 ( Figure 2) includes a helical tube 24 ( Figures 19-20). Adjacent sections in its helical geometry can be opened or closed (compressed) to adjust the cross sectional stiffness of the inner tubular section 12 of the sheath assembly 2. As depicted in Figures 2 and 6-7, a linear path or track 30 is provided in the outer tube hub 16 which cooperates with the actuating mechanism or drive slide 18. As shown in Figures 2 and 8-9, the mechanism 18 is secured in a "soft" position.
- Figures 3-4 the actuating mechanism 18 is depicted in a proximal position.
- Figure 3 illustrates the outer tube 22.
- Figure 4 illustrates a helical embodiment of the stiffening component 20, in which the helix is shown in an open position.
- Figures 5-7 depict the actuating mechanism 18 in a distal, or "stiff position.
- the helical tube stiffening component 20 is shown with the outer tube 22 hidden, and the helix is in a "closed” condition.
- a proximal end region of the stiffening component 20 is attached to the actuating mechanism 18, which moves the stiffening component 20 distally and proximally in a linear motion.
- the sliding mechanism 18 moves the stiffening component 20 distally and proximally in a linear motion.
- the actuating mechanism 18 moves the stiffening component 20 distally and proximally in a linear motion.
- the sliding mechanism 18 is in the proximal position, the helix is open, thereby creating a "soft" tubular section.
- the sliding mechanism is in a distal position, the helix is closed, thereby creating a "stiff tubular section.
- a suitable material for helical sections or strips of the tube stiffening component reinforcing member 20 is a polymer like TEFLON or a shape memory material, such as a nickel titanium alloy like NITINOL.
- Locating features such as locking detents 38, 40 can be provided in many forms.
- Figures 8-9 they are shown as a male/female hemispherical or arched form. They may also take the form of a snapping fixture on the actuating mechanism 18 which snaps into a mating detail in the outer tube hub 16. They may also take the form of a ratcheting-type design, with a pawl on the sliding mechanism 18 that locks into a ratcheting detail on the outer tube hub 16 or vice-versa. With either design, the pawl could be pressed and held open to return to the "soft" position. There are multiple ways to lock the sliding mechanism 18 in the "soft" and “stiff” positions. Only one form is shown in Figures 8-9.
- the actuating mechanism 18 incorporates a tracking tab 42 which slides in a linear track 30 provided in the outer tube hub 16.
- the track 30 and tab 42 interface to permit a smooth motion and transition of linear force to the stiffening component 20.
- Embodiment #2 Braided Stiffening Component with Linear Slide
- the stiffening component 20 in this embodiment, comprises a braided or stranded wire or mesh 44 arranged in a tubular configuration.
- the braided geometry is such that openings between the individual strands can be opened and closed through linear motion.
- the changing density of the open 46 and closed 48 positions adjusts the cross sectional stiffness of the tubular section of the component 20, thereby creating a "soft" ( Figure 10) and "stiff ( Figure 11) condition.
- the stiffening component 20 includes flexible strands of interwoven spirally-oriented filaments that form a cylindrical braid. As tension is applied to the stiffening component 20 by the actuating mechanism 18, the component 20 tends to become stiffer.
- the component 20 in one embodiment optionally has an opening at each end that fits over the inner tube 12.
- the stiffening component 20 contracts radially as it is stretched longitudinally. In use, when a tensile force is applied to the proximal end of the stiffening component 20 and that force is opposed at the distal end so as to stretch the stiffening component 20, it will constrict in the transverse direction, thereby increasingly more tightly gripping the inner tube 12 as increasing longitudinal forces are applied.
- the strands are made of a resilient, substantially non-elastic material such as a polymer or nickel-titanium alloy. Other materials such as a braided polymer ( Figures 10-11) may also be deployed, additionally or alternatively.
- the strands are helically positioned and each individual strand preferably has a circular or oval cross- section.
- the component 20 includes a cylindrical woven braid that has been drawn down snuggly upon and along at least a portion of the inner tube 12 by longitudinal tension.
- the proximal end 9 of the stiffening component 20 is attached to the actuating mechanism 18, which moves the stiffening component 20 distally and proximally in a linear motion.
- the sliding mechanism 18 moves the stiffening component 20 distally and proximally in a linear motion.
- the braided wire is open, thereby creating a "soft" tubular section.
- the braided strands are relatively closed ( Figure 11), thereby creating a "stiff tubular section.
- Figures 13, 13 A, 15, 15 A the outer tube 22 is hidden.
- Embodiment #3 Rotational Sliding Mechanism
- the actuating mechanism 18 is changed from linear motion to rotational or helical motion.
- Rotational motion can be used with the helical stiffening component 20 (Embodiment #1).
- Rotational motion will "wind up" the helix 50 of the tube stiffening component 20 ( Figures 18-20), thereby changing its cross sectional stiffness.
- motion of the actuating mechanism 18 is primarily helical.
- Helical displacement can be used with the helical tube stiffening component (Embodiment #1) and the braided tube stiffening component (Embodiment #2).
- the helical motion will "wind up" the helix 50 of the tube stiffening component 20, thereby changing its cross sectional stiffness.
- Linear motion 15 of the helical travel compresses and decompresses the braided wire 44, thereby changing its cross sectional stiffness.
- helical motion of the sliding mechanism 18 is counterclockwise to accommodate a surgeon's desired practices. Most surgeons are trained to use a clockwise rotational motion when inserting a sheath into the vessel. By using a counterclockwise motion for stiffening the sheath, the potential for accidental engagement of the actuating mechanism 18 will be reduced. This is depicted in Figures 18-20. From Figure 20, the drive slide 18 is removed. That figure is a more detailed view that depicts the helix 50 that is provided in the outer tube hub
- a safety mechanism is depicted in Figures 21-26.
- a safety feature 54 can optionally be incorporated into the rotational handle 52 or outer tube hub 16.
- the safety mechanism 54 could be incorporated into any of the design components, if desired.
- the safety mechanism 54 is depicted as a removable, disposable component. In use, the safety mechanism 54 would be removed prior to operating the slide mechanism 18.
- a side view is depicted in Figure 24; a sectional view of the side view is in Figure 25; and a top view appears in Figure 26; and a sectional view of the top view appears in Figure 27, in which the safety feature 54 has been removed.
- Figures 28-29 are cross sectional views that depict optional details of the distal end of the sheath assembly 2. Illustrated in Figures 28-29 are the inner tube 12, outer tube 22, helically cut tube 24, and the cavity 28 that lies between the inner and outer tubes. It will be appreciated that in Figure 9, the helically cut tube 24 could be replaced in some embodiments by a braided form of stiffening component 20.
- sheaths that are for example 19, 23-25, 45, 50 or 65 cm in length. The length is selected based upon the insertion site and the anatomical area to be treated — e.g., insertion below the knee, the carotid artery, etc. Following is a list of reference numerals and the structural components to which they refer that are used in this disclosure:
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Biomedical Technology (AREA)
- Pulmonology (AREA)
- Engineering & Computer Science (AREA)
- Anesthesiology (AREA)
- Biophysics (AREA)
- Heart & Thoracic Surgery (AREA)
- Hematology (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Media Introduction/Drainage Providing Device (AREA)
- Surgical Instruments (AREA)
Abstract
An endovascular sheath apparatus 2 is provided. The endovascular sheath apparatus 2 includes an inner tube 12 that includes a lumen 26 for introducing medical fluids or devices and an outer surface. The apparatus 2 further includes an outer tube 22 with an interior surface. The outer and inner surfaces define a cavity 28 therebetween. The apparatus 2 still further includes a stiffening component 20 that is at least partially received in at least part of the cavity 28. An actuating mechanism 18 cooperates with the stiffening component 20. A method of providing intravascular delivery of a sheath includes the steps of providing an inner tube 12; positioning a stiffening component 20 around the inner tube 12; and deploying an actuating mechanism 18 that cooperates with the stiffening component 20, a stiffness characteristic of which being adjustable extra-corporeally by movement of the actuating mechanism in combination with the stiffening component.
Description
ENDOVASCULAR SHEATH WITH GRADABLE STIFFNESS DEVICE AND METHOD
BACKGROUND OF THE INVENTION
1. Field of the Invention
The invention relates to a sheath device with gradable stiffness and method that reduces or prevents buckling when inserted into a vascular tract.
2. Background Art
Endo vascular surgery has developed as a form of minimally invasive surgery that is used to access many regions of the body through major blood vessels. Conventionally, a catheter is introduced through the skin into a large blood vessel such as the femoral artery or vein. Often, the catheter carries a radio-opaque dye that can be detected by X-ray or fluororscopic procedures. Endovascular surgery is becoming more widely used because it is minimally invasive and offers immediate advantages over more traditional, yet highly invasive surgeries.
Generally stated, a catheter is a tube that can be inserted into a body cavity, duct or vessel. Catheters typically allow drainage or the injection of a fluid or access by surgical instruments. Many uses require that the catheter be thin and flexible (a "soft" catheter or tube); in other cases it may be a larger solid tube — a "hard" catheter.
As used herein, (1) the term "sheath" refers to the outer covering of a guide wire. Unless the context dictates otherwise, it may be used interchangeably with the term "catheter," and (2) the term "guide wire" refers to a long and flexible fine spring that is used to introduce and position an intravascular catheter. Conventionally, the catheter or sheath is often threaded over the wire — the wire may then be withdrawn, leaving the catheter in place, as taught by the Seldinger technique, a medical procedure that is used to obtain access to blood vessels and other hollow
organs. Seldinger Sl (Catheter Replacement of the Needle in Percutaneous Arteriography; a New Technique). Acta Radiologica (5); 368-76 (1953).
During interventional vascular procedures, situations may arise where a catheter needs to be advanced through tortuous paths, in which it may be difficult to steer a guide wire or other interventional device along the interstices a vessel. For example, one area in the vascular geometry that causes issues related to advancing a device is the interface of the femoral and aortic vessels. During peripheral procedures, the entry location for devices is the femoral artery on the side of the body opposite the area of concern. The device must then pass over the femoral arch and into the opposite femoral artery. When the interventional devices used during the procedure advance towards such tortuous anatomy, buckling of the device often occurs at the femoral/aortic interface. Typically, conventional interventional devices tend to buckle under the axial force reaction of the tortuous vessel to the pressures of insertion. Buckling of the device often occurs proximal to the tortuous anatomy.
There are several reasons why this situation is difficult to overcome with current technology:
1. The geometry of a guide wire. A guide wire must have some flexibility to be able to steer through the vascular anatomy without dissecting a vessel. A guide wire is typically a small diameter wire (.014") and is pliable and soft. When the guide wire is advanced through any tortuous anatomy, due to the small size of the wire, the wire has little ability to resist buckling. The proximal section of the wire typically buckles, and very little if any force is transmitted to the distal end of the wire.
2. The flexibility of the guiding catheter or sheath. Guiding catheters and sheaths are conventionally made from reinforced extruded plastic tubing. These devices are soft and generally provide little resistance to buckling.
3. The intervention devices that are used during the procedure. The intervention devices (e.g. stent delivery systems and balloons) are pliable along their axial shaft, and easily buckle when an axial force is applied.
Most devices and techniques that are available do not provide a solution to the buckling that occurs when tortuous anatomy is encountered during a procedure. If a device can not be advanced through this tortuous anatomy, the procedure may not be able to be performed, and the outcome for the patient may be compromised.
It is known that when the leading edge of a sheath encounters a tight lesion, there is a loss of kinetic energy. Some approaches solve this problem by using a hydrophilic material that is applied to the sheath. The problem with this approach, however, is that the surgeon's hands tend to slip over the outside surface of the sheath.
Among the U.S. and foreign patent documents that were considered before filing this application are the following: EP131632; EP171682; WO98/5644; US 5,599,326; 7,226,466; 7,273,487; 20060235502; 20060258987; 20060264907; 20070049899; 20080045895; 20080172037.
SUMMARY OF THE INVENTION
Against this background it would be desirable to have a sheath device with a simple design, that is easy to use in patients that require an interventional vascular procedure. Preferably, such a sheath device would be intuitive to use and require minimal surgical finesse, yet be able to negotiate a tortuous path that may include calcified lesions and fibrosed areas, swiftly and with repeatability if desired without disrupting adjacent tissue.
Preferably, the disclosed sheath device reduces the risk of vascular perforation by offering a tip design that does not ablate tissue ahead of its distal end, thereby avoiding inadvertent rupture of tissue that may be inadvertently contacted.
In one aspect, the invention includes a device and method that reduces or prevents unwanted buckling of interventional devices. The inventive device allows the transmission of axial forces through the interventional devices to the distal end of the product without kinking or buckling.
It would be desirable to have a differential level of stiffness along the length of a sheath. For example, the distal region of the sheath would desirably be fluffy or soft. This would reduce the risk of trauma that might otherwise be caused by interference between the distal end of the sheath and a tight turn in an arterial wall.
Preferably, the surgeon would like to be able to determine without interchanging sheaths whether a particular sheath would be stiff or not stiff (compliant) an intermediate region or in a region proximate its distal end. Thus, one aspect of the invention includes a sheath that has a changing modulus of elasticity along its length. In some embodiments, the sheath may have a modulus of elasticity along its length that could be discretely or gradually changed.
Another facet of the invention is the provision of a sheath that has the capability to change its outside diameter along its length so that, for example, the outside diameter may be less at the distal than at the proximal end. These facets may also have applicability to designing a stent.
To meet these needs, an endovascular sheath apparatus is provided that comprises an inner tube which includes a lumen for introducing medical fluids or devices and an outer surface. Disposed outside the inner tube is an outer tube that has an interior surface. The respective outer and inner surfaces define a cavity therebetween. A stiffening component is at least partially received in at least part of the cavity. Cooperating with the stiffness component is an actuating mechanism.
BRIEF DESCRIPTION OF THE DRAWINGS
FIGURE 1 is an overall perspective, exploded view of several aspects of the invention (Embodiment #1);
FIGURE 2 depicts a proximal position of a sliding mechanism (isometric view) when the device is in a "soft" position;
FIGURE 3 depicts a proximal position of a sliding mechanism with an outer tube (side elevation view);
FIGURE 4 depicts a proximal position of the sliding mechanism with a helical tube stiffening component (side elevational view);
FIGURE 5 depicts a distal portion of the sliding mechanism in a "stiff position (isometric view);
FIGURE 6 depicts a proximal position of the sliding mechanism including the outer tube (side elevation view);
FIGURE 7 depicts a proximal position of the sliding mechanism with the helical tube stiffening component, in which the outer tube is hidden and in which a helix is configured in a closed condition (side elevation view);
FIGURE 8 depicts a slide mechanism that cooperates with locking detents for "soft" and "stiff" positions (sectioned, isometric view);
FIGURE 9 depicts a sliding mechanism including an outer tube hub sliding track, in which a tracking tab is shown in a sliding position and a linear track is provided in an outer tube hub (sectioned, isometric view);
FIGURE 10 depicts a braided wire or polymeric mesh in an open position (Embodiment #2);
FIGURE 11 depicts the braided wire or polymeric mesh in a closed configuration;
FIGURE 12 depicts a proximal position of the sliding mechanism and outer tube (side elevational view);
FIGURES 13 and 13A depict a proximal position of the sliding mechanism that cooperates with an embodiment of a braided tube stiffening component, with the outer tube hidden (side elevation view);
FIGURE 14 depicts a distal position of the sliding mechanism, in which the outer tube is shown (side elevation view);
FIGURES 15 and 15A depict a proximal position of the sliding mechanism with the braided tube stiffening component, in which the outer tube is hidden (side elevation view);
FIGURE 16 depicts an "open" position ("soft") of a rotational handle (Embodiment #3, side elevation view);
FIGURE 17 depicts this embodiment with the rotational handle rotated to a "stiff position ("closed"; side elevation view);
FIGURE 18 depicts an "open" position ("soft") of the helical rotation handle (Embodiment #4, side elevation view);
FIGURE 19 depicts a helical rotation in which the handle has moved
(with both rotational and linear movement) to a "stiff position ("closed");
FIGURE 20 depicts a helical track in the outer tube hub (isometric view);
FIGURE 21 depicts an optional safety mechanism that prevents accidental movement of the sliding mechanism (side elevation view);
FIGURE 22 depicts the safety mechanism in a "locked" position;
FIGURE 23 depicts the safety mechanism in an "unlocked" position;
FIGURE 24 is a side elevational view of the embodiment of Figure 23;
FIGURE 25 is a longitudinal sectional view of the embodiment of Figure 24 taken along the line XXV-XXV thereof;
FIGURE 26 is a top view thereof;
FIGURE 27 is a sectional view of the embodiment of Figure 26 taken along the line XXVII-XXVII thereof;
FIGURE 28 depicts additional sectional detail of a distal end region of the shaft; and
FIGURE 29 is an enlarged portion thereof.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT(S)
Turning first to Figures 1-3 of the drawings, there is depicted an endo vascular sheath apparatus 2 that has an inner tube 12 which includes a lumem 26 for introducing medical devices or fluids. The inner tube 12 has an outer surface 13 (best seen in Figures 28-29.) Positioned outside the inner tube 12 is an outer tube 22 that has an interior surface 23. Lying between the inner 23 and outer 13 surfaces is a cavity 28. At least a portion of the cavity 28 houses a stiffening component 20 that reinforces at least a portion of the inner tube 12 to minimize or prevent kinking. In cooperation with the stiffening component 20, there is provided an actuating mechanism 18. The cavity 28 lies between the inner 12 and outer 22 tubes for placement of a tube stiffening component 20.
As used herein, the terms "proximal" and "distal" describe the opposing axial ends of the endovascular sheath assembly 2 as well as the axial ends of a medical device with which the sheath is used, and its components. The term "proximal" refers to the end of the member (or component) that is closest to the surgeon during use. Conversely, the term "distal" refers to the end of the member (or component) that is
positioned closest to the end of the sheath assembly 2 that is initially inserted into the vascular system.
In its environment of use, the endovascular sheath 2 may include an inner tube hub 10 (Figures 1-2), the proximal section of which it may if desired be attached to a valve system 6. In one embodiment, the valve system 6 may serve as a one-way valve 14 by which fluid or device may be ducted into the inner tube 12. If desired, the one-way valve 6 may be incorporated into the inner tube hub 10. As illustrated in Figures 1-9, a hub section 10 optionally lies at an interface of the sheath assembly 2 with other interventional devices 4. In each design contemplated (Figures 1-29), the one-way valve 14 may optionally serve as a secondary piece. This valve prevents the flow of blood out of the device, but allows the introduction of interventional devices (guide catheters, wires, etc.) into the vasculature. It may also be a multiple piece design with a removable valve. The proximal section also optionally has a luer lock connection for flushing the device or injecting fluids into the system such as contrast-providing media.
Preferably, the outer tube 22 provides a smooth exterior surface to facilitate navigation along tortuous and possibly narrowing channels in the vascular system. In practice, a bond 15 (Figure 28) may be provided at a distal region of the outer tube 22 in order to affix it to the inner tube 12.
If desired, an outer tube hub 16 (Figures 1-2) may be attached to the outer tube 22. The outer tube hub 16 attaches to the inner tube hub 10.
Continuing with primary reference to Figures 6-9, the outer tube hub 16 provides a track 30 that guides in one embodiment the linear displacement of an actuating or sliding mechanism 18. Preferably, the track 30 defines one or more locating features which in the embodiment depicted in Figure 8 include a detent 40 (distal, stiff) and a position 38 (proximal, soft). In the embodiment of Figure 9, a tracking tab 42 is guided along the track 30 that is provided in the outer tube hub 16. If desired, the actuating mechanism 18 maybe positioned at an intermediate location if the surgeon desires the inner tube 12 to have a stiffness which is intermediate
between that which results from positioning the actuating mechanism at locations 40 or 38.
It will thus be appreciated that the actuating mechanism 18 communicates with a stiffening component 20 (Figures 10-11) and interfaces with the outer tube hub 16 (Figures 1-2). The stiffening component 20 has a distal end 8 that is affixed by bond 15 to the inner tube 12 at one end and to the actuating mechanism
18 at a proximal end of the stiffening component 20.
The inner tube 12 of the sheath assembly 2 conventionally includes a reinforced tubular section that is typically made of an extruded plastic. It is soft and pliable. The distal tip is preferably extremely soft to reduce the possibility of any vessel damage when the device 2 is introduced into an artery, such as the femoral artery. In one embodiment of the disclosed invention, the body of the inner tubular section 12 is reinforced with the stiffening component 20, such as a braided material, preferably made of metal or strands of a plastic material. This helps prevent the tubular section 12 from susceptibility 60 being kinked, and gives a selective stiffening characteristic to the device 2 that resists buckling.
One objective of the inventive design is to retain the functionality of the current products on the market, but give the interventionalist a sheath assembly 2 that has adjustable stiffness when required or desirable during the procedure.
The inventive design incorporates variations in the stiffening component 20 of the sheath assembly 2. These variations help stiffen the body of the inner tubular section 12 of the sheath. This stiffening allows the interventionalist to more easily transmit axial force when desired to the distal end 8 of the device, thereby facilitating the passage of the device 2 through a tortuous anatomy.
There are at least four alternative embodiments of the inventive concept:
Embodiment #1 : Helical Stiffening Component with Linear Slide
In this embodiment, the stiffening component 20 (Figure 2) includes a helical tube 24 (Figures 19-20). Adjacent sections in its helical geometry can be opened or closed (compressed) to adjust the cross sectional stiffness of the inner tubular section 12 of the sheath assembly 2. As depicted in Figures 2 and 6-7, a linear path or track 30 is provided in the outer tube hub 16 which cooperates with the actuating mechanism or drive slide 18. As shown in Figures 2 and 8-9, the mechanism 18 is secured in a "soft" position.
In Figures 3-4, the actuating mechanism 18 is depicted in a proximal position. Figure 3 illustrates the outer tube 22. Figure 4 illustrates a helical embodiment of the stiffening component 20, in which the helix is shown in an open position.
Figures 5-7 depict the actuating mechanism 18 in a distal, or "stiff position. In Figure 7, the helical tube stiffening component 20 is shown with the outer tube 22 hidden, and the helix is in a "closed" condition.
In one example, a proximal end region of the stiffening component 20 is attached to the actuating mechanism 18, which moves the stiffening component 20 distally and proximally in a linear motion. When the sliding mechanism 18 is in the proximal position, the helix is open, thereby creating a "soft" tubular section. When the sliding mechanism is in a distal position, the helix is closed, thereby creating a "stiff tubular section.
In one embodiment, a suitable material for helical sections or strips of the tube stiffening component reinforcing member 20 is a polymer like TEFLON or a shape memory material, such as a nickel titanium alloy like NITINOL.
Locating features such as locking detents 38, 40 (Figures 8-9) can be provided in many forms. In one embodiment (Figure 8) they are shown as a male/female hemispherical or arched form. They may also take the form of a
snapping fixture on the actuating mechanism 18 which snaps into a mating detail in the outer tube hub 16. They may also take the form of a ratcheting-type design, with a pawl on the sliding mechanism 18 that locks into a ratcheting detail on the outer tube hub 16 or vice-versa. With either design, the pawl could be pressed and held open to return to the "soft" position. There are multiple ways to lock the sliding mechanism 18 in the "soft" and "stiff" positions. Only one form is shown in Figures 8-9.
In the embodiment of Figure 9 the actuating mechanism 18 incorporates a tracking tab 42 which slides in a linear track 30 provided in the outer tube hub 16. The track 30 and tab 42 interface to permit a smooth motion and transition of linear force to the stiffening component 20. The stiffening component
20 can be fixed to the tracking tabs 42 on the sliding mechanism 18.
Additional design variations of the sliding mechanism 18 and tube stiffening component 20 are described below.
Embodiment #2: Braided Stiffening Component with Linear Slide
In this embodiment, the stiffening component 20 (Figures 10- 13A) in this embodiment comprises a braided or stranded wire or mesh 44 arranged in a tubular configuration. The braided geometry is such that openings between the individual strands can be opened and closed through linear motion. The changing density of the open 46 and closed 48 positions adjusts the cross sectional stiffness of the tubular section of the component 20, thereby creating a "soft" (Figure 10) and "stiff (Figure 11) condition.
In one approach, the stiffening component 20 includes flexible strands of interwoven spirally-oriented filaments that form a cylindrical braid. As tension is applied to the stiffening component 20 by the actuating mechanism 18, the component 20 tends to become stiffer. The component 20 in one embodiment optionally has an opening at each end that fits over the inner tube 12. The stiffening component 20 contracts radially as it is stretched longitudinally. In use, when a tensile force is applied to the proximal end of the stiffening component 20 and that force is opposed
at the distal end so as to stretch the stiffening component 20, it will constrict in the transverse direction, thereby increasingly more tightly gripping the inner tube 12 as increasing longitudinal forces are applied. Preferably, the strands are made of a resilient, substantially non-elastic material such as a polymer or nickel-titanium alloy. Other materials such as a braided polymer (Figures 10-11) may also be deployed, additionally or alternatively. In cross-section, in one embodiment, the strands are helically positioned and each individual strand preferably has a circular or oval cross- section. Thus, the component 20 includes a cylindrical woven braid that has been drawn down snuggly upon and along at least a portion of the inner tube 12 by longitudinal tension.
As shown in Figures 10- 15 A, the proximal end 9 of the stiffening component 20 is attached to the actuating mechanism 18, which moves the stiffening component 20 distally and proximally in a linear motion. When the sliding mechanism 18 is in the proximal position (Figure 10) the braided wire is open, thereby creating a "soft" tubular section. When the sliding mechanism 18 is in the distal position, the braided strands are relatively closed (Figure 11), thereby creating a "stiff tubular section. In Figures 13, 13 A, 15, 15 A, the outer tube 22 is hidden.
Embodiment #3: Rotational Sliding Mechanism
In this embodiment (Figures 16, 17), the actuating mechanism 18 is changed from linear motion to rotational or helical motion. Rotational motion can be used with the helical stiffening component 20 (Embodiment #1). Rotational motion will "wind up" the helix 50 of the tube stiffening component 20 (Figures 18-20), thereby changing its cross sectional stiffness.
In Figure 16, the rotational handle 52 is shown in the "open" position. In Figure 17, the rotational handle 52 is shown as having been rotated to a "closed" or "stiff position.
Embodiment #4: Helical Actuating Mechanism
In this embodiment (Figures 18-20), motion of the actuating mechanism 18 is primarily helical. Helical displacement can be used with the helical tube stiffening component (Embodiment #1) and the braided tube stiffening component (Embodiment #2). The helical motion will "wind up" the helix 50 of the tube stiffening component 20, thereby changing its cross sectional stiffness. Linear motion 15 of the helical travel compresses and decompresses the braided wire 44, thereby changing its cross sectional stiffness.
In a preferred embodiment, helical motion of the sliding mechanism 18 is counterclockwise to accommodate a surgeon's desired practices. Most surgeons are trained to use a clockwise rotational motion when inserting a sheath into the vessel. By using a counterclockwise motion for stiffening the sheath, the potential for accidental engagement of the actuating mechanism 18 will be reduced. This is depicted in Figures 18-20. From Figure 20, the drive slide 18 is removed. That figure is a more detailed view that depicts the helix 50 that is provided in the outer tube hub
16.
One form of a safety mechanism is depicted in Figures 21-26. To prevent accidental movement of the sliding mechanism 18, a safety feature 54 can optionally be incorporated into the rotational handle 52 or outer tube hub 16. The safety mechanism 54 could be incorporated into any of the design components, if desired. In the embodiment shown, the safety mechanism 54 is depicted as a removable, disposable component. In use, the safety mechanism 54 would be removed prior to operating the slide mechanism 18. A side view is depicted in Figure 24; a sectional view of the side view is in Figure 25; and a top view appears in Figure 26; and a sectional view of the top view appears in Figure 27, in which the safety feature 54 has been removed.
Figures 28-29 are cross sectional views that depict optional details of the distal end of the sheath assembly 2. Illustrated in Figures 28-29 are the inner tube 12, outer tube 22, helically cut tube 24, and the cavity 28 that lies between the inner
and outer tubes. It will be appreciated that in Figure 9, the helically cut tube 24 could be replaced in some embodiments by a braided form of stiffening component 20.
Depending on the application, alternative embodiments of the invention include sheaths that are for example 19, 23-25, 45, 50 or 65 cm in length. The length is selected based upon the insertion site and the anatomical area to be treated — e.g., insertion below the knee, the carotid artery, etc. Following is a list of reference numerals and the structural components to which they refer that are used in this disclosure:
While embodiments of the invention have been illustrated and described, it is not intended that these embodiments illustrate and describe all possible forms of the invention. Rather, the words used in the specification are words of description rather than limitation, and it is understood that various changes may be made without departing from the spirit and scope of the invention.
Claims
1. An endovascular sheath apparatus comprising: an inner tube that includes a lumen for introducing medical fluids or devices and an outer surface; an outer tube with an interior surface, the outer and inner surfaces defining a cavity therebetween; a stiffening component that is at least partially received in at least part of the cavity; an actuating mechanism that cooperates with the stiffening component.
2. The sheath apparatus of claim 1, further including: an inner tube hub that is attached to a proximal end of the inner tube.
3. The sheath apparatus of claim 2, also having: a valve system detachably connected to the proximal hub.
4. The sheath apparatus of claim 1, further comprising: a bond between the inner and outer surfaces of the outer and inner tubes.
5. The sheath apparatus of claim 1, further including: an outer tube hub that is attached to a proximal end of the outer tube.
6. The sheath apparatus of claim 5, wherein the outer tube hub includes: a track that cooperates with the actuating mechanism.
7. The sheath apparatus of claim 6, wherein the track and the actuating mechanism define one or more locating features that position the actuating mechanism and the stiffening component in relation to the outer tube hub.
8. The sheath apparatus of claim 7, wherein the actuating mechanism optionally locks or moves into or through multiple positions provided by the locating features to provide a soft or stiff sheath or one of intermediate stiffness.
9. The sheath apparatus of claim 1, wherein the stiffening component has an adjustable cross section with a stiffness characteristic that is influenced by the actuating mechanism, the stiffness component being fixed to the inner tube at a distal end and attached to the actuating mechanism at a proximal end of the stiffening component so that upon moving distally and proximally, the actuating mechanism adjusts a stiffness characteristic of the stiffening component.
10. The sheath apparatus of claim 1, wherein the stiffening component comprises a material selected from the group consisting of a stranded metal, a stranded polymer, and a helical tube.
11. The sheath apparatus of claim 10, wherein the stranded metal includes a shape memory material.
12. The sheath apparatus of claim 11 , wherein the shape memory material includes a nickel-titanium alloy.
13. The sheath apparatus of claim 6, wherein the track has a configuration that is selected from the group consisting of linear, helical, and combinations thereof.
14. The sheath apparatus of claim 7, wherein the locating features are selected from the group consisting of male-female hemispherical features, male-female arched features, and ratcheting features.
15. The sheath apparatus of claim 10, wherein the stiffening component includes an interwoven assembly of filaments wherein the filaments define a cris-crossing array that define a generally cylindrical surface.
16. The sheath apparatus of claim 15, wherein the cylindrical surface has an internal diameter that decreases in response to a longitudinal force that is applied in tension to the stiffening component and increases in response to a longitudinal force that is applied in compression to the stiffening component.
17. The sheath apparatus of claim 1, wherein the actuating mechanism includes a handle by which longitudinal or rotational or combined longitudinal and rotational force can be applied to the actuating mechanism.
18. The sheath apparatus of claim 17, wherein the actuating mechanism includes a track that guides the handle in a counterclockwise direction when viewed from a proximal end of the sheath apparatus.
19. The sheath apparatus of claim 1, further including a safety mechanism that includes a clip that is detachably removable from a channel defined in the outer tube hub.
20. The sheath apparatus of claim 1 , wherein the sheath apparatus has a length that has a dimension selected from the group consisting of 19, 23-25, 45, 50, 60 and 90 - 100 cm.
21. A method of guiding a sheath through a vascular passageway, the method comprising the steps of: inserting a proximal end of the sheath into a vascular structure; and adjusting the stiffness of at least a portion of the sheath by axial tensioning of a stiffening component located coaxially over an inner tube of the sheath to selectively stiffen at least a portion of the inner tube.
22. The method of claim 21 wherein the adjusting step comprises stiffening the inner tube when additional column strength is needed to overcome an obstruction or constriction in the vascular passageway.
23. The method of claim 21 wherein the adjusting step comprises reducing the stiffness of the inner tube when the sheath is being pushed through a tortuous part of the vascular system.
24. The method of claim 21 wherein the amount of axial tensioning is varied while the sheath is being pushed through the vascular passageway.
25. A method of providing intravascular delivery of a sheath, comprising steps of: providing an inner tube; positioning a stiffening component around the inner tube; and deploying an actuating mechanism that cooperates with the stiffening component, a stiffness characteristic of which being adjustable extra-corporeally by movement of the actuating mechanism in combination with the stiffening component.
Priority Applications (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
EP09816717A EP2326380A4 (en) | 2008-09-23 | 2009-09-18 | Endovascular sheath with gradable stiffness device and method |
CN2009801467051A CN102223909A (en) | 2008-09-23 | 2009-09-18 | Endovascular sheath with gradable stiffness device and method |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US12/235,894 US8663196B2 (en) | 2008-09-23 | 2008-09-23 | Endovascular sheath with gradable stiffness device and method |
US12/235,894 | 2008-09-23 |
Publications (1)
Publication Number | Publication Date |
---|---|
WO2010036560A1 true WO2010036560A1 (en) | 2010-04-01 |
Family
ID=42038395
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US2009/057380 WO2010036560A1 (en) | 2008-09-23 | 2009-09-18 | Endovascular sheath with gradable stiffness device and method |
Country Status (4)
Country | Link |
---|---|
US (1) | US8663196B2 (en) |
EP (1) | EP2326380A4 (en) |
CN (1) | CN102223909A (en) |
WO (1) | WO2010036560A1 (en) |
Cited By (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9439653B2 (en) | 2011-12-07 | 2016-09-13 | Traumatek Solutions B.V. | Devices and methods for endovascular access and therapy |
US10118020B2 (en) | 2011-12-07 | 2018-11-06 | Traumatek Solutions B.V. | Devices and methods for endovascular access and therapy |
US10987488B2 (en) | 2015-06-23 | 2021-04-27 | Traumatek Solutions, B.V. | Vessel cannulation device and method of use |
Families Citing this family (21)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP2379129B1 (en) | 2008-12-23 | 2017-09-13 | Silk Road Medical, Inc. | Methods and systems for treatment of acute ischemic stroke |
US9060773B2 (en) * | 2011-12-16 | 2015-06-23 | Covidien Lp | Occlusive implant delivery devices and associated methods |
US9044575B2 (en) * | 2012-10-22 | 2015-06-02 | Medtronic Adrian Luxembourg S.a.r.l. | Catheters with enhanced flexibility and associated devices, systems, and methods |
US10548663B2 (en) | 2013-05-18 | 2020-02-04 | Medtronic Ardian Luxembourg S.A.R.L. | Neuromodulation catheters with shafts for enhanced flexibility and control and associated devices, systems, and methods |
US10953193B2 (en) * | 2013-07-16 | 2021-03-23 | Covidien Lp | Microcatheter with modified PTFE liner |
US9265512B2 (en) | 2013-12-23 | 2016-02-23 | Silk Road Medical, Inc. | Transcarotid neurovascular catheter |
US9241699B1 (en) | 2014-09-04 | 2016-01-26 | Silk Road Medical, Inc. | Methods and devices for transcarotid access |
EP3174591B1 (en) * | 2014-07-28 | 2023-11-15 | Silk Road Medical, Inc. | Transcarotid neurovascular catheter |
JP7082052B2 (en) | 2015-09-03 | 2022-06-07 | ネプチューン メディカル インク. | A device for advancing the endoscope in the small intestine |
US10441746B2 (en) * | 2015-09-04 | 2019-10-15 | Petrus A. Besselink | Flexible and steerable device |
JP6964134B2 (en) | 2016-07-13 | 2021-11-10 | パーヒューズ・リミテッド | Highly flexible, kinking resistant catheter shaft |
WO2018035452A1 (en) | 2016-08-18 | 2018-02-22 | Neptune Medical | Device and method for enhanced visualization of the small intestine |
EP3925638A1 (en) | 2017-12-15 | 2021-12-22 | Perfuze Limited | Improved catheters and devices and systems incorporating such catheters |
EP3801187B1 (en) | 2018-05-31 | 2024-02-07 | Neptune Medical Inc. | Device for enhanced visualization of the small intestine |
JP2021531111A (en) | 2018-07-19 | 2021-11-18 | ネプチューン メディカル インク. | Dynamic hardening medical composite structure |
US11793392B2 (en) | 2019-04-17 | 2023-10-24 | Neptune Medical Inc. | External working channels |
CN110124179B (en) * | 2019-05-20 | 2024-07-23 | 王奎重 | Interventional catheter with adjustable hardness and changeable head end direction |
CN110916746B (en) * | 2020-02-18 | 2020-07-14 | 上海介入医疗器械有限公司 | Pusher and intervene conveying system |
CN115666676A (en) | 2020-03-30 | 2023-01-31 | 海王星医疗公司 | Laminar wall for rigidifying device |
US11937778B2 (en) | 2022-04-27 | 2024-03-26 | Neptune Medical Inc. | Apparatuses and methods for determining if an endoscope is contaminated |
CN115956864A (en) * | 2023-01-31 | 2023-04-14 | 湖南省华芯医疗器械有限公司 | Rigidity-adjustable negative pressure suction sheath, insertion part and endoscope |
Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4516972A (en) * | 1982-01-28 | 1985-05-14 | Advanced Cardiovascular Systems, Inc. | Guiding catheter and method of manufacture |
US20040049157A1 (en) * | 2001-09-13 | 2004-03-11 | Michael Plishka | Paracentesis device having multiple detachable components |
US20060106447A1 (en) * | 2004-01-26 | 2006-05-18 | Nmt Medical, Inc. | Adjustable stiffness medical system |
US20060270980A1 (en) * | 2001-04-18 | 2006-11-30 | B. Braun Melsungen A.G. | Safety spring catheter introducer assembly |
Family Cites Families (19)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5290229A (en) * | 1991-07-15 | 1994-03-01 | Paskar Larry D | Transformable catheter and method |
US5599326A (en) | 1994-12-20 | 1997-02-04 | Target Therapeutics, Inc. | Catheter with multi-layer section |
US5730723A (en) * | 1995-10-10 | 1998-03-24 | Visionary Medical Products Corporation, Inc. | Gas pressured needle-less injection device and method |
US5938653A (en) | 1997-06-09 | 1999-08-17 | Scimed Life Systems, Inc. | Catheter having controlled flexibility and method of manufacture |
US6511471B2 (en) * | 2000-12-22 | 2003-01-28 | Biocardia, Inc. | Drug delivery catheters that attach to tissue and methods for their use |
US7226466B2 (en) | 2001-09-06 | 2007-06-05 | Nmt Medical, Inc. | Flexible delivery system |
US6960188B2 (en) | 2001-11-30 | 2005-11-01 | Abbott Laboratories Vascular Entities Limited | Catheter having enhanced distal pushability |
US7115134B2 (en) | 2002-07-22 | 2006-10-03 | Chambers Technology, Llc. | Catheter with flexible tip and shape retention |
US7309334B2 (en) * | 2002-07-23 | 2007-12-18 | Von Hoffmann Gerard | Intracranial aspiration catheter |
US7273485B2 (en) | 2003-03-20 | 2007-09-25 | Advanced Cardiovascular Systems, Inc. | Balloon catheter having a shaft with a variable stiffness inner tubular member |
US7273487B1 (en) | 2003-12-18 | 2007-09-25 | Advanced Cardiovascular Systems, Inc. | Balloon catheter having a multilayered shaft with variable flexibility |
US20060129130A1 (en) * | 2004-11-18 | 2006-06-15 | Tal Michael G | Sheath/catheter system with controlled hardness and flexibility |
US20060184105A1 (en) | 2005-02-15 | 2006-08-17 | Townsend Gregory L | Thin wall catheter and method of placing same |
US7828832B2 (en) | 2005-04-18 | 2010-11-09 | Medtronic Vascular, Inc. | Intravascular deployment device with improved deployment capability |
US20060264907A1 (en) | 2005-05-02 | 2006-11-23 | Pulsar Vascular, Inc. | Catheters having stiffening mechanisms |
US20060258987A1 (en) | 2005-05-10 | 2006-11-16 | Cook Incorporated | Catheter stiffening member |
US7998132B2 (en) * | 2005-09-02 | 2011-08-16 | Boston Scientific Scimed, Inc. | Adjustable stiffness catheter |
US7993303B2 (en) | 2006-04-21 | 2011-08-09 | Abbott Laboratories | Stiffening support catheter and methods for using the same |
US20080172037A1 (en) | 2006-11-01 | 2008-07-17 | Percutaneous Systems, Inc. | Catheter with adjustable column stability and methods for its use |
-
2008
- 2008-09-23 US US12/235,894 patent/US8663196B2/en not_active Expired - Fee Related
-
2009
- 2009-09-18 EP EP09816717A patent/EP2326380A4/en not_active Withdrawn
- 2009-09-18 WO PCT/US2009/057380 patent/WO2010036560A1/en active Application Filing
- 2009-09-18 CN CN2009801467051A patent/CN102223909A/en active Pending
Patent Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4516972A (en) * | 1982-01-28 | 1985-05-14 | Advanced Cardiovascular Systems, Inc. | Guiding catheter and method of manufacture |
US20060270980A1 (en) * | 2001-04-18 | 2006-11-30 | B. Braun Melsungen A.G. | Safety spring catheter introducer assembly |
US20040049157A1 (en) * | 2001-09-13 | 2004-03-11 | Michael Plishka | Paracentesis device having multiple detachable components |
US20060106447A1 (en) * | 2004-01-26 | 2006-05-18 | Nmt Medical, Inc. | Adjustable stiffness medical system |
Non-Patent Citations (1)
Title |
---|
See also references of EP2326380A4 * |
Cited By (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9439653B2 (en) | 2011-12-07 | 2016-09-13 | Traumatek Solutions B.V. | Devices and methods for endovascular access and therapy |
US10118020B2 (en) | 2011-12-07 | 2018-11-06 | Traumatek Solutions B.V. | Devices and methods for endovascular access and therapy |
US10124144B2 (en) | 2011-12-07 | 2018-11-13 | Traumatek Solutions, B.V. | Devices and methods for endovascular access and therapy |
US11154690B2 (en) | 2011-12-07 | 2021-10-26 | Traumatek Solutions, B.V. | Devices and methods for endovascular access and therapy |
US10987488B2 (en) | 2015-06-23 | 2021-04-27 | Traumatek Solutions, B.V. | Vessel cannulation device and method of use |
Also Published As
Publication number | Publication date |
---|---|
CN102223909A (en) | 2011-10-19 |
US20100076405A1 (en) | 2010-03-25 |
US8663196B2 (en) | 2014-03-04 |
EP2326380A4 (en) | 2011-12-07 |
EP2326380A1 (en) | 2011-06-01 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US8663196B2 (en) | Endovascular sheath with gradable stiffness device and method | |
US11771867B2 (en) | Suction catheter systems for applying effective aspiration in remote vessels, especially cerebral arteries | |
US9023011B2 (en) | Medical device | |
US9393041B2 (en) | Expandable medical access sheath | |
US5843031A (en) | Large-diameter introducer sheath having hemostasis valve and removable steering mechanism | |
JP7155269B2 (en) | Guided extension catheter | |
US20080172037A1 (en) | Catheter with adjustable column stability and methods for its use | |
US20070260225A1 (en) | Steerable sheath actuator | |
US20090281500A1 (en) | Devices, system and methods for minimally invasive abdominal surgical procedures | |
US20070021648A1 (en) | Transluminal sheath hub | |
AU2005254572A1 (en) | Steerable vascular sheath | |
WO2005061039A1 (en) | Modular steerable sheath catheters | |
JP2013514149A (en) | Approach device and method of using the same | |
JP2008520375A (en) | System and method for lumen access | |
US20080097296A1 (en) | Removable hub assembly for medical device | |
US20090281376A1 (en) | Devices, system and methods for minimally invasive abdominal surgical procedures | |
CA3078311A1 (en) | Steerable device and system | |
US11344702B2 (en) | Steerable sheath | |
WO2015146408A1 (en) | Catheter assembly and inner catheter | |
US20090281498A1 (en) | Devices, system and methods for minimally invasive abdominal surgical procedures | |
JP2022507926A (en) | Guide extension catheter | |
US20110251595A1 (en) | Endovascular catheter and method with hydraulic bladder system | |
US20230293860A1 (en) | Balloon Tipped Dual Lumen Tapered Guide Extension Catheter |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
WWE | Wipo information: entry into national phase |
Ref document number: 200980146705.1 Country of ref document: CN |
|
121 | Ep: the epo has been informed by wipo that ep was designated in this application |
Ref document number: 09816717 Country of ref document: EP Kind code of ref document: A1 |
|
DPE1 | Request for preliminary examination filed after expiration of 19th month from priority date (pct application filed from 20040101) | ||
WWE | Wipo information: entry into national phase |
Ref document number: 2009816717 Country of ref document: EP |
|
NENP | Non-entry into the national phase |
Ref country code: DE |
|
WWE | Wipo information: entry into national phase |
Ref document number: 2783/DELNP/2011 Country of ref document: IN |