Patent Application
20140163421
The present disclosure relates generally to catheters for navigating through the human vasculature, and in particular, to improved catheter tip designs and reinforced sections of the catheter.
Intravascular ultrasound (IVUS) imaging is widely used in interventional cardiology as a diagnostic tool for assessing a vessel, such as an artery, within the human body to determine the need for treatment, to guide intervention, and/or to assess its effectiveness. An IVUS imaging system uses ultrasound echoes to form a cross-sectional image of the vessel of interest. Typically, IVUS imaging uses a transducer carried by an IVUS catheter that both emits ultrasound signals (waves) and receives the reflected ultrasound signals. The emitted ultrasound signals (often referred to as ultrasound pulses) pass easily through most tissues and blood, but they are partially reflected by discontinuities arising from tissue structures (such as the various layers of the vessel wall), red blood cells, and other features of interest. The IVUS imaging system, which is connected to the IVUS catheter by way of a patient interface module, processes the received ultrasound signals (often referred to as ultrasound echoes) to produce a cross-sectional image of the vessel where the IVUS catheter is located.
Short guide wire lumen rapid exchange (RX) catheter designs or “monorail” designs generally employ a much shorter guide wire lumen at the distal end of the catheter, typically in the range from about 1 cm to 4 cm. The transducer may then be disposed axially spaced but close to the guide wire lumen, allowing a reduction in the total cross-sectional area of the catheter. Among the difficulties sometimes encountered with short tipped guide wire catheters is the possibility that the distal end or tip of the catheter may kink as it is advanced through the patient's vasculature. The unwanted bending may occur in the region of a guide wire side port, irrigation port, or any unsupported region distal region of the imaging system sheath. Kinking is the result of a deformation of the distal tip and usually is characterized by a sharp deformation or point bend of the very distal section of the catheter. Such a deformation may result from attempting to pass the distal tip through a very tortuous vascular section. Parts of the catheter may also kink or bend back upon itself in a condition referred to as prolapse. Thereafter, the catheter may return to its original shape, or it may remain permanently deformed if, during the bending, catheter material is bent beyond its elastic limit.
Once the catheter has been kinked, the performance of the catheter is substantially degraded. Higher friction will be encountered at the location of the kink, adversely affecting torque transmission, as well as making it more difficult to advance the catheter over the guide wire.
The transition between the proximal section and the distal section of the catheter should also provide a good transition in flexibility from the relatively stiff proximal section to the relatively flexible distal section to facilitate tracking the catheter within the patient's tortuous vasculature. One difficulty has been that catheter junctions often result in a lump, step, or other surface irregularity in the bond junction.
Therefore, a need exists for catheters that are resistant to kinking or prolapse when introduced through tortuous regions of blood vessels.
The present disclosure provides improved structural arrangements for the distal portion of intravascular devices, including intravasvascular imaging devices. In particular, the constructions of the present disclosure result in intravascular devices having improved handling characteristics due to the combination of flexibility and resistance to kinking or prolapse when introduced through tortuous regions of blood vessels.
The present disclosure provides various embodiments of a distal tip construction for use in intravascular ultrasound (IVUS) imaging. An exemplary tip construction includes three layers. The first layer is an inner layer adjacent to a guide wire lumen, the second layer is a middle layer adjacent the inner layer, and the third layer is an outer layer adjacent the middle layer. The first layer typically includes a lubricious polymer to promote low friction and ease of tracking over the guide wire. The second layer generally includes a polymer that adheres well to both the inner and outer layers. The third layer usually includes a polymer that is flexible and that can also be coated with a hydrophilic coating. This construction provides low friction and good guide wire movement, along with reduced friction between the catheter and blood vessel wall.
In other embodiments, the sheath includes a flexible portion having a lumen for receiving an ultrasound probe and a distal portion that includes a flexible tip. The tip defines a guide wire lumen having a distal guide wire opening and a proximal guide wire opening through a sidewall. An area between the proximal guide wire entry opening and the flexible proximal portion is supported to prevent prolapse. In some embodiments, the area is supported by a tube, which may comprise a polyimide and/or stainless steel. In alternative embodiments, the tube includes an inner lumen in communication with the ultrasound lumen and a flush hole through the tube. The sheath provides a flexible device that is locally reinforced between the proximal guide wire entry opening and ultrasound probe so that the monorail is flexible, tracks well, and does not prolapse. The additional support prevents localized kinking.
The present disclosure further provides methods for forming catheter body junctions. The methods include providing first and second elongated catheter shaft portions of different diameters to be bonded, placing a sleeve of material similar to the first or second shaft portions over a junction between the two shaft portions, placing a heat shrink thermoplastic sleeve around the junction of the first and second shaft portions, heating the assembly such that the heat shrink thermoplastic sleeve shrinks and constrains a flow of sleeve material at the junction. The heat shrink thermoplastic sleeve is removed after cooling. The use of the thermoplastic sleeve helps to strengthen and improve the thermally bonded catheter junctions. The methods provide a smooth transition over the entire length of the bond junction.
Both the foregoing general description and the following detailed description are exemplary and explanatory in nature and are intended to provide an understanding of the present disclosure without limiting the scope of the present disclosure. In that regard, additional aspects, features, and advantages of the present disclosure will become apparent to one skilled in the art from the following detailed description.
Aspects of the present disclosure are best understood from the following detailed description when read with the accompanying figures. It is emphasized that, in accordance with the standard practice in the industry, various features are not drawn to scale. In fact, the dimensions of the various features may be arbitrarily increased or reduced for clarity of discussion. In addition, the present disclosure may repeat reference numerals and/or letters in the various examples. This repetition is for the purpose of simplicity and clarity and does not in itself dictate a relationship between the various embodiments and/or configurations discussed.
For the purposes of promoting an understanding of the principles of the present disclosure, reference will now be made to the embodiments illustrated in the drawings, and specific language will be used to describe the same. It is nevertheless understood that no limitation to the scope of the disclosure is intended. Any alterations and further modifications to the described devices, systems, and methods, and any further application of the principles of the present disclosure are fully contemplated and included within the present disclosure as would normally occur to one skilled in the art to which the disclosure relates. In particular, it is fully contemplated that the features, components, and/or steps described with respect to one embodiment may be combined with the features, components, and/or steps described with respect to other embodiments of the present disclosure. For the sake of brevity, however, the numerous iterations of these combinations will not be described separately.
Referring specifically to
The probe 100 comprises a sheath and a transducer shaft surrounded by the sheath. The transducer shaft is flushed with a sterile fluid, such as saline, within the catheter body. The fluid serves to eliminate the presence of air pockets or bubbles around the transducer shaft that adversely affect image quality. The fluid can also act as a lubricant.
The distal portion 110 of the sheath is inserted into a patient during the operation of the probe 100. The distal portion 110 includes a short tip. With short tips, only the very distal end of the catheter follows the guide wire, while the remainder of the catheter is left to move as needed within a blood vessel. The short tip in illustrated embodiment is about 22-23 mm compared to about 22 cm for most other long tipped coronary RX catheters. In one embodiment, the tip is 23 mm.
The transition portion 120 of the sheath is typically only about 1-3 mm, but is typically not supported by a guide wire like the tip, or by the transducer shaft like the proximal portion 130. In one embodiment, the transition portion 120 is only about 3 mm in length and has a diameter of about 3.2 French (F) or about 1 mm. Thus, in prior designs this unsupported area is prone to kinking or prolapse.
The proximal portion 130 of the sheath and the proximal end portion of the transducer shaft are connected to an interface module. The rotation of the transducer shaft within the catheter body is controlled by the interface module, which provides a plurality of user interface controls that can be manipulated by a user. The interface module can receive, analyze, and/or display information received through the transducer shaft.
The usable length of the probe 100 (the portion that can be inserted into a patient) can be any suitable length and can be varied depending upon the application. The overall dimensions of the catheter will depend on use, with the length varying widely, typically being between about 40 cm and 150 cm, usually being between about 40 cm and 120 cm for peripheral catheters and being between about 110 cm and 150 cm for coronary catheters. The diameter of the catheter body may also vary widely, with the diameter of the distal portion 110 typically being between about 2 F and 4 F, and the diameter of the proximal portion 130 typically being about 3 F and 6 F. In an exemplary embodiment, the diameter of the proximal portion 130 is 3.5 F.
Turning now to
In one embodiment, proximal guide wire exit opening 250 includes a flush hole 252 to allow saline to flow out of the ultrasound probe lumen 235 in the direction of arrow F. In an alternative embodiment, a separate flush hole (not shown) is formed through support tube 280 and outer tube 290 opposite the guide wire exit opening.
The ultrasound probe lumen 235 may extend from the proximal end of the sheath 200 to the distal tip thereof, but will usually be terminated before reaching the distal tip. Thus, the guide wire lumen 218 may be disposed at least partially adjacent to the ultrasound probe lumen 235.
The distal tip portion 210 is coupled to the transition portion 220 and the proximal portion 230 by adhesive bonding 254. As illustrated, transition portion 220 and proximal portion 230 include the outer tube 290 that defines the ultrasound probe lumen 235. Within the transition portion 220 is support tube 260 to help support the transition portion 220 during use. The support tube 260 provides stiffness and controlled bending of the sheath 200 in the region proximal the proximal guide wire exit opening 250 and distal the ultrasound probe 270. As shown in
The ultrasound probe 270 is located at an end of a flexible transducer drive shaft that spins inside the sheath 200 inserted into the vessel of interest. The ultrasound probe 270 is usually oriented such that the ultrasound signals propagate generally perpendicular to an axis of the catheter. In the typical rotational catheter, the fluid-filled (e.g., saline-filled) sheath 290 protects the vessel tissue from the spinning probe and shaft while permitting ultrasound signals to freely propagate from the probe into the tissue and back. As the shaft rotates (for example, at 30 revolutions per second), the probe is periodically excited with a high voltage pulse to emit a short burst of ultrasound. The ultrasound signals are emitted from the probe, through the fluid-filled sheath and sheath wall, in a direction generally perpendicular to an axis of rotation of the shaft. The same probe then listens for returning ultrasound signals reflected from various tissue structures, and the imaging system assembles a two dimensional image of the vessel cross-section from a sequence of several hundred of these ultrasound pulse/echo acquisition sequences occurring during a single revolution of the probe.
Turning back to
In one embodiment, the length of the distal tip 210 is about 22 mm. In an alternative embodiment, the length of the tip is less than about 3 cm.
The inner layer 212 includes a lubricious polymer that slides easily over guide wire 255. In an exemplary embodiment, the lubricious polymer includes a high-density polyethylene to promote low friction and ease of tracking over the guide wire 255.
The middle layer 214 includes a polymer that adheres to the inner layer 212 and the outer layer 216. In an exemplary embodiment, the polymer includes a functionalized or maleic anhydride grafted polyethylene.
The outer layer 216 includes a flexible polymer. In an exemplary embodiment, the flexible polymer includes a polyether block amide and/or polyamide. The flexible polymer can make tight or tortuous bends in the anatomy. In a further aspect, the outer layer 216 can be coated with a polymeric hydrophilic coating to reduce tracking friction against vessel walls in the anatomy.
The transition portion 220 includes support tube 260. The support tube 260 is located in an area between the proximal guide wire opening 250 and the flexible proximal portion 230. The support tube 260 may be positioned within a distal extremity of the lumen 235. The support tube 260 is formed of any material suitable to reinforce the transition portion 220 so that the transition portion 220 is supported and does not prolapse. In an exemplary embodiment, the support tube 260 includes polyimide and/or stainless steel. In an embodiment, the support tube 260 includes an inner lumen in communication with the ultrasound probe lumen 235 and a flush hole 252 through at least a portion of the support tube 260. Without limitation to support members having alternative lengths, in the illustrated embodiment, the support member 260 has a length between 1-3 mm. In a further aspect, the support member 260 has a length of approximately 2 mm.
The sheath 200 of the present disclosure has excellent ability to track within the patient's tortuous vasculature due to the improved design of the distal tip portion 210 and the reinforced transition portion 220.
The outer sheath 290 may be formed from a single tubular member that extends the entire distance from the proximal portion 130 to the distal portion 110 or may be formed from two or more tubular members that are joined together. The two tubular members may be joined together so that they share a common inner lumen. As shown in
Referring now to
Bonding of the subassembly is completed by applying heat to the subassembly melt the catheter portions and sleeve. During heating, the heat shrink thermoplastic sleeve 340 shrinks and constrains a flow of the sleeve material 330 and catheter materials at the junction 315. During the heating, the sleeve material 330 melts and fuses the two shaft portions 310, 320 together. The sleeve material 330 flows and fills in around the junction 315 to form a transition zone 360. After cooling, the heat shrink thermoplastic sleeve 340 is removed.
Referring now to
Persons skilled in the art will recognize that the devices and methods described above can be modified in various ways. Accordingly, persons of ordinary skill in the art will appreciate that the embodiments encompassed by the present disclosure are not limited to the particular exemplary embodiments described above. In that regard, although illustrative embodiments have been shown and described, a wide range of modification, change, and substitution is contemplated in the foregoing disclosure. It is understood that such variations may be made to the foregoing without departing from the scope of the present disclosure. Accordingly, it is appropriate that the appended claims be construed broadly and in a manner consistent with the present disclosure.
The present application claims priority to and the benefit of U.S. Provisional Patent Application No. 61/734,286, filed Dec. 6, 2012, which is hereby incorporated by reference in its entirety.
| Number | Date | Country | |
|---|---|---|---|
| 61734286 | Dec 2012 | US |
