TUBULAR LARGE BORE TRANSSEPTAL CROSSING SHEATH

Abstract

Disclosed is an electrically enabled introducer sheath, such as for crossing a septum into a left atrium and guiding a large bore catheter across the septum and into the left atrium. The sheath includes an elongate, flexible tubular body, having a proximal end, a distal end and an electrically conductive sidewall defining a central lumen. A tubular insulation layer surrounds the sidewall and leaves exposed an annular conductive surface at the distal end. The tubular body has a proximal hub, having at least one access port in communication with the central lumen and a connector in electrical communication with the conductive sidewall. The central lumen is configured to receive a radio frequency conducting wire, to facilitate crossing the septum.

Claims

1. An electrically enabled introducer sheath, comprising: an elongate, flexible tubular body, having a proximal end, a distal end and an electrically conductive sidewall defining a central lumen; a tubular insulation layer surrounding the sidewall and leaving exposed an annular conductive surface at the distal end; and a proximal hub on the tubular body, having at least one access port in communication with the central lumen and a connector in electrical communication with the conductive sidewall.

2. An electrically enabled introducer sheath as in claim 1, wherein the sidewall comprises a stainless steel tube.

3. An electrically enabled introducer sheath as in claim 1, wherein the annular conductive surface faces in a distal direction.

4. An electrically enabled introducer sheath as in claim 1, wherein the distal end comprises at least one distal extension configured to enhance delivered energy density.

5. An electrically enabled introducer sheath as in claim 1, comprising at least four distal projections.

6. An electrically enabled introducer sheath as in claim 1, wherein the distal end comprises a scalloped surface.

7. An electrically enabled introducer sheath as in claim 1, having an outside diameter of about 0.050 inches.

8. An electrically enabled introducer sheath as in claim 7, having an inside diameter sufficient to receive a 0.035 inch guidewire.

9. An electrically enabled introducer sheath as in claim 8, which in combination with an 0.035 inch guidewire has sufficient structural integrity to guide a large bore catheter transvascularly trough a septal wall and into a left atrium of the heart.

10. An electrically enabled introducer sheath as in claim 9, wherein the large bore catheter has an inside diameter sufficient to receive the introducer sheath therethrough.

11. An electrically enabled introducer sheath as in claim 1, having an outside diameter of at least about 0.040 inches.

12. An electrically enabled introducer sheath as in claim 1, having an outside diameter of at least about 0.045 inches.

13. An electrically enabled introducer sheath as in claim 8, which in combination with an 0.035 inch guidewire has sufficient structural integrity to guide a large bore catheter transvascularly trough a septal wall and into a left atrium of the heart.

14. An electrically enabled introducer sheath as in claim 1, which exhibits sufficient structural integrity to guide a large bore catheter transvascularly trough a septal wall and into a left atrium of the heart.

15. An electrically enabled introducer sheath as in claim 14, in which no part of the electrically conductive sidewall is a braided or woven wire.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

[0018] FIG. 1 schematically illustrates a transseptal crossing system in accordance with the present invention.

[0019] FIG. 2 is a side elevational view of an RF needle in accordance with the present invention.

[0020] FIG. 2A is a cross section taken along the line A-A in FIG. 2.

[0021] FIG. 2B is a detail view of the distal tip of the needle in FIG. 2.

[0022] FIG. 3 is a cross sectional view through the needle of FIG. 2.

[0023] FIG. 4A-4C are detail views of the distal energy delivery tip of one implementation of the invention.

[0024] FIG. 5A-5C are detail views of the distal energy delivery tip of another implementation of the invention.

[0025] FIG. 6 is a schematic cross section of a portion of a human heart, having a transseptal crossing system of the present invention positioned in the right atrium.

[0026] FIG. 7 is a view as in FIG. 6, showing positioning of the distal tip of the transseptal crossing system at the fossa ovalis.

[0027] FIG. 8 shows penetration of the guidewire and cannula through the fossa ovalis.

[0028] FIG. 9 shows penetration of the large bore sheath and dilator crossing the fossa ovalis.

[0029] FIG. 10 shows the large bore sheath in position across the septum with the dilator and other system components removed to provide access to the left atrium.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT

[0030] FIG. 1 illustrates an embodiment of a tissue penetrating apparatus 102 in a transseptal crossing system 100. Apparatus 102 comprises an elongate tubular body 104 having a distal region 106, and a proximal region 108. Distal region 106 is adapted to be inserted within and along a lumen of a body of a patient, such as a patient's vasculature, and maneuverable therethrough to a desired location proximate material, such as tissue, to be perforated.

[0031] In some embodiments, the tubular body 104 may have at least one lumen extending from proximal region 108 to distal region 106 such as lumen 208 shown in FIG. 2A. Tubular body 104 may be constructed of a biocompatible polymer material jacket typically with a metal core that provides column strength to apparatus 102. The tubular body 104 is sufficiently stiff to permit a dilator 84 and a large bore guiding sheath 12 (See FIG. 6) to be easily advanced over apparatus 102 and through a perforation. Examples of suitable materials for the tubular portion of tubular body 104 are stainless steel, nitinol, polyetheretherketone (PEEK), nylon, and polyimide. In the illustrated embodiment, the outer diameter along the tubular portion of tubular body 104 may taper down to distal region 106. In alternate embodiments, the outer diameter along tubular body 104 remains substantially constant from proximal region 108 to distal region 106.

[0032] Distal region 106 comprises a softer polymer material with an optional embedded braid or coil so that it is pliable and atraumatic when advanced through vasculature. In some embodiments, the material is also formable (e.g., Nitinol or stainless steel with a polymer jacket), so that its shape can be changed during manufacturing, typically by exposing it to heat while it is fixed in a desired shape. In an alternate embodiment, the shape of distal region is modifiable by the operator during use. An example of a suitable plastic is PEBAX (a registered trademark of Atofina Chemicals, Inc.). In the present embodiment, the distal region 106 comprises a curve portion 115.

[0033] As the distal region 106 is advanced out of a guiding sheath, it may have a preset curve so that it curls away from the general axis of the sheath which helps ensure that energy delivery tip 112 is not in a position to inadvertently injure unwanted areas within a patient's heart after trans-septal perforation. Curve length may be about 4 cm (about 1.57″) to about 6 cm (about 2.36″) and the curve may traverse about 225 to about 315 degrees of the circumference of a circle. For example, the curve may be about 5 cm in length and may traverse about 270 degrees of the circumference of a circle. Such an embodiment may be useful to avoid unwanted damage to cardiac structures.

[0034] In some embodiments, curve portion 115 begins about 0.5 cm to about 1.5 cm proximal to energy delivery device 112, leaving an approximately 1 cm (about 0.39″) straight portion in the distal region 106 of apparatus 102. This ensures that this initial portion of apparatus 102 will exit dilator 84 (see FIG. 6) without curving, enabling the operator to easily position the apparatus 102, for example, against a septum as described further below. This feature further ensures that the distal region 106 of apparatus 102 will not begin curving within the atrial septum.

[0035] Distal region 106 may have a smaller outer diameter compared to the remainder of tubular body 104 so that dilation of a perforation is limited while the distal region 106 is advanced through the perforation. Limiting dilation seeks to ensures that the perforation will not cause hemodynamic instability once apparatus 102 is removed. In some embodiments, the outer diameter of distal region 106 may be no larger than about 0.8 mm to about 1.0 mm. For example, the outer diameter of distal region 106 may be about 0.9 mm (about 0.035″). This is comparable to the distal outer diameter of the trans-septal needle that is traditionally used for creating a perforation in the atrial septum. Similarly, in some embodiments, the outer diameter of tubular body 104 may be no larger than about 0.040″ to about 0.060″. For example, the outer diameter of tubular body 104 may be about 0.050″ (1.282 mm), which is also comparable to the trans-septal needle dimensions.

[0036] Distal region 106 terminates at functional tip region 110, which comprises an energy delivery component and optionally also as an ECG measuring device. Functional tip region 110 comprises at least one energy delivery tip 112 made of a conductive and optionally radiopaque material, such as stainless steel, tungsten, platinum, or another metal. One or more radiopaque markings may be affixed to tubular body 104 to highlight the location of the transition from distal region 106 to the remainder of tubular body 104, or other important landmarks on apparatus 102. Alternately, the entire distal region 106 of apparatus 102 may be radiopaque. This can be achieved by filling the polymer material, for example PEBAX, used to construct distal region 106 with radiopaque filler. An example of suitable radiopaque filler is Bismuth. Distal region 106 may contain at least one opening 109 which is in fluid communication with main lumen 200 (FIG. 2A) as described further below.

[0037] In the illustrated embodiment, proximal region 108 comprises a hub 114, to which are attached a catheter connector cable 116, and connector 118. Tubing 117 and adapter 119 are attached to hub 114 as well. Proximal region 108 may also have one or more depth markings 113 to indicate distances from functional tip region 110, or other important landmarks on apparatus 102. Hub 114 comprises a curve direction or orientation indicator 111 that is located on the same side of apparatus 102 as the curve 115 in order to indicate the direction of curve 115. Orientation indicator 111 may comprise inks, etching, or other materials that enhance visualization or tactile sensation. One or more curve direction indicators may be used and they may be of any suitable shape and size and a location thereof may be varied about the proximal region 108.

[0038] In the illustrated embodiment, adapter 119 is configured to releaseably couple apparatus 102 to an external pressure transducer 121 via external tubing 123. External pressure transducer 121 is coupled to a monitoring system 125 that converts a pressure signal from external pressure transducer 121 and displays pressure as a function of time. Catheter connector cable 116 may connect to an optional Electro-cardiogram (ECG) interface unit via connector 118. An optional ECG connector cable connects an ECG interface unit to an ECG recorder, which displays and captures ECG signals as a function of time. A generator connector cable may connect the ECG interface unit to an energy source such as a generator (not illustrated). In this embodiment, the ECG interface unit can function as a splitter, permitting connection of the electrosurgical tissue piercing apparatus 102 to both an ECG recorder and generator simultaneously. ECG signals can be continuously monitored and recorded and the filtering circuit within the ECG interface unit and may permit energy, for example RF energy, to be delivered from generator 128 through electrosurgical apparatus 102 without compromising the ECG recorder.

[0039] In another embodiment (not shown) of apparatus 102, there may be a deflection control mechanism associated with the distal region 106 of apparatus 102 and an operating mechanism to operate said control mechanism associated with the proximal region 108 of apparatus 102. One or two or more pull wires may extend from a proximal control to the distal region 106 to actively deflect the distal region 106 as will be understood in the art. The control mechanism may be used to steer or otherwise actuate at least a portion of distal region 106.

[0040] Generator 128 may be a radiofrequency (RF) electrical generator that is designed to work in a high impedance range. Because of the small size of energy delivery tip 112 the impedance encountered during RF energy application is very high. General electrosurgical generators are typically not designed to deliver energy in these impedance ranges, so only certain RF generators can be used with this device. In one embodiment, the energy is delivered as a continuous wave at a frequency between about 400 kHz and about 550 kHz, such as about 460 kHz, a voltage of between 100 to 200 V RMS and a duration of up to 99 seconds. A grounding pad 130 is coupled to generator 128 for attaching to a patient to provide a return path for the RF energy when generator 128 is operated in a monopolar mode.

[0041] Other embodiments could use pulsed or non-continuous RF energy. Some embodiments for pulsed radio frequency energy have radio frequency energy of not more than about 60 watts, a voltage from about 200 Vrms to about 400 Vrms and a duty cycle of about 5% to about 50% at about from slightly more than 0 Hz to about 10 Hz. More specific embodiments include radio frequency energy of not more than about 60 watts, a voltage from about 240 Vrms to about 300 Vrms and a duty cycle of 5% to 40% at 1 Hz, with possibly, the pulsed radio frequency energy being delivered for a maximum of 10 seconds. In one example, the generator can be set to provide pulsed radio frequency energy of not more than about 50 watts, a voltage of about 270 Vrms, and a duty cycle of about 10% at 1 Hz. Alternatively, the pulsed radio frequency energy could comprise radio frequency energy of not more than about 50 watts, a voltage of about 270 Vrms, and a duty cycle of about 30% at 1 Hz.

[0042] In still other embodiments of apparatus 102, different energy sources may be used, such as radiant (e.g. laser), ultrasound, thermal or other frequencies of electrical energy (e.g. microwave), with appropriate energy sources, coupling devices and delivery devices depending upon the desired clinical performance.

[0043] Additional details of the tissue penetration apparatus 102 are described in connection with FIG. 2. Referring to FIGS. 2 and 2A, the tubular body 104 comprises a cannula 206 such as a 0.050″ cannula having a central lumen 208 extending therethrough. The lumen 208 is dimensioned to slidably receive a guide wire 210 such as an 0.035″ guidewire. In certain implementations of the invention, it may be desirable to electrically isolate the guide wire 210 from the cannula 206. This may be accomplished by providing a tubular insulation layer 212 positioned between the guide wire 210 and the cannula 206. In the illustrated embodiment, the insulation layer 212 comprises a coating or tubular sleeve surrounding the guide wire 210. A further tubular insulation layer 214 may be provided on the outside of the cannula 206 to electrically isolate the cannula 206 from the patient.

[0044] Referring to FIG. 2B, there is illustrated a detail view of the distal end 202 of cannula 206, having a guide wire 210 extending therethrough. The guide wire 210 may comprise a pigtail or other curved distal end as is understood in the art.

[0045] Referring to FIG. 3, the tissue penetrating apparatus 102 may additionally be provided with a Y connector 220, having a proximal guide wire access port 222 and a flush port 224 in communication with the distal region 106 such as via exit port 109 (FIG. 1) or cannula 206 central lumen 208. The Y connector 220 may be provided with a distal first connector 226 configured to cooperate with a second complementary connector 228 on the proximal end of the hub 114. First connector 226 and second connector 228 may be complementary components of a standard luer connector as is understood in the art. Alternatively, the hub 114 and Y connector 220 may be formed as an integral unit.

[0046] FIGS. 4A-4C illustrate the axial slidability of the guidewire 210 within the cannula 206. In FIG. 4C, the guidewire has been proximally retracted into the central lumen 208 so that the leading surface of the system is an annular charge transfer surface 207, which comprises a distal end face of the cannula 206. The insulation layer 214 on cannula 206 may extend distally all the way to the edge of the end face of the cannula 206, or to no more than 2 mm or 1 mm or less proximally of the end face of the cannula 206. The system thus permits delivering RF energy from either the guidewire alone, or the cannula alone or both, depending upon the desired clinical performance.

[0047] The separately insulated cannula 206 and guidewire can be configured to deliver bipolar electricity to the distal tip. The cannula 206 can be used as the ground path and replace the body pad or other electrode, which may provide desirable impedance characteristics depending upon the desired clinical performance.

[0048] FIGS. 5A-5C illustrate a modified distal end face of the cannula 206.

[0049] At least one distal extension 220 is carried by the cannula 206, to provide a site of enhanced energy density on the leading charge transfer surface 207 carried by the projection 220. At least two or four or more projections 220 may be provided, such as 10 as illustrated in FIG. 5B, creating scalloped surface with a plurality of circumferentially spaced apart distal transfer surfaces 207.

[0050] One method of delivering a large bore catheter in a single pass using the transseptal puncture system of the present invention may be as follows. [0051] 1. Advance a guidewire (GW) into the superior vena cava (SVC) and deliver a large bore catheter (e.g., left atrial appendage occlusion device; mitral valve repair or replacement; intra atrial adjustable annuloplasty device) with a dilator to the SVC. [0052] 2. Withdraw GW inside of the dilator. [0053] 3. Withdraw the large bore sheath and the dilator down to the right atrium. [0054] 4. Steer the sheath and dilator into position in the interatrial septum, specifically tenting the septum with the dilator. [0055] 5. Deliver the cannula and GW into position with the cannula extending distally beyond the dilator and the GW distally beyond the cannula and in contact with the fossa ovalis. 5a. If necessary for positioning purposes, withdraw cannula proximal to the bend of the steerable sheath, then step 6. [0056] 6. Activate the distal tip of the GW with RF energy, and pass the GW through the septum and into the left atrium (LA). [0057] 7. Drive the cannula, dilator and sheath distally through the septum and into the LA. [0058] 8. If the cannula cannot pass through the septum into the LA, activate the distal tip of the cannula with RF energy and advance the cannula into the LA. [0059] 9. Drive the dilator and the large bore sheath over the access cannula and into the LA. [0060] 10. Withdraw the cannula and dilator, and introduce the index procedure catheter through the large bore sheath.

[0061] As will be appreciated by those of skill in the art, the GW and cannula can alternatively be simultaneously operated in monopolar mode; either the GW or cannula can be energized separately; or the GW and cannula can be operated in bipolar mode, depending upon the desired clinical performance.

[0062] Thus, referring to FIG. 6, there is illustrated a schematic cross-section of a portion of the heart 10. The right atrium 86 is in communication with the inferior vena cava 88 and the superior vena cava 90. The right atrium 86 is separated from the left atrium 16 by the intraatrial septum 18. The fossa ovalis 92 is located on the intraatrial septum 18. As seen in FIG. 6, a large bore transseptal sheath 12 may have a dilator 84, both riding over the cannula 206 and guidewire 210, all positioned within the right atrium 86.

[0063] The combination of the sheath 12 with the dilator 84 having the transseptal cannula 206 and GW 210 extending distally therefrom, is then drawn proximally from the superior vena cava while a curved section of the sheath, alone or in combination with a preset curve at the distal region of dilator 84 and or cannula 206, causes the tip of the cannula—GW combination to “drag” along the wall of the right atrium 86 and the septum 18, by proximal traction until the tip pops onto the fossa ovalis 92, as shown in FIG. 7.

[0064] After the tip of the cannula—GW combination has been placed in the desired location against the fossa ovalis 92, RF energy is applied via the tip of the transseptal GW 210 to allow the GW 210 to pass through the septum into the LA. As previously described, RF energy may also be delivered via the distal end of the cannula 206 if desired. See FIGS. 8 and 9.

[0065] One medical technique is to confirm the presence of the tip of the transseptal GW 210 within the left atrium 16. Confirmation of such location of the tip of the transseptal GW 210 may be accomplished by monitoring the pressure sensed through a transseptal GW lumen or an annular lumen defined between the GW 210 and the inside surface of the cannula 206 central lumen to ensure that the measured pressure is within the expected range and has a waveform configuration typical of left atrial pressure. Alternatively, proper position within the left atrium 16 may be confirmed by analysis of oxygen saturation level of the blood drawn through an available lumen; i.e., aspirating fully oxygenated blood. Finally, visualization through fluoroscopy alone, or in combination with the use of dye, may also serve to confirm the presence of the tip of the transseptal cannula 206 and GW 210 in the left atrium 16.

[0066] After placing the transseptal cannula tip within the left atrium 16, the tip of the dilator 84 is advanced through the septum 18 and into the left atrium 16, as shown in FIG. 9. When the tapered tip of dilator 84 appears to have entered the left atrium 16, the transseptal cannula 206 may be withdrawn. The large bore sheath 12 may then be advanced into the left atrium 16, either by advancing the sheath 12 alone over the dilator 84 or by advancing the sheath 12 and dilator 84 in combination. The dilator 84 may then be withdrawn from sheath 12 when the latter has been advanced into the left atrium, thus leaving the main lumen of sheath 12 as a clear pathway to advancing further large bore diagnostic or therapeutic instruments into the left atrium.