Delivery systems for VfA cardiac therapy

Abstract

An implantable medical device delivery system includes a delivery catheter including an elongated body with a first portion defining a first lumen and a second portion defining a second lumen. An angle is defined between a first axis and a second axis defined by the first and second portions, respectively. The second axis points toward the left ventricular (LV) apex of the patient's heart when the first axis points into the CS. The first portion or an elongated element may extend into the CS to anchor the delivery catheter to the orientation of the CS.

Description

The present disclosure relates to implantable medical devices, systems, and methods. In particular, the present disclosure relates to delivery of implantable medical devices, systems, and methods for cardiac therapy, including single chamber or multiple chamber pacing (e.g., dual or triple chamber pacing), atrioventricular synchronous pacing, asynchronous pacing, triggered pacing, cardiac resynchronization pacing, or tachycardia-related therapy.

The cardiac conduction system includes the sinus atrial (SA) node, the atrioventricular (AV) node, the bundle of His, bundle branches and Purkinje fibers. A heart beat is initiated in the SA node, which may be described as the natural “pacemaker” of the heart. An electrical impulse arising from the SA node causes the atrial myocardium to contract. The signal is conducted to the ventricles via the AV node which inherently delays the conduction to allow the atria to stop contracting before the ventricles begin contracting thereby providing proper AV synchrony. The electrical impulse is conducted from the AV node to the ventricular myocardium via the bundle of His, bundle branches, and Purkinje fibers.

Patients with a conduction system abnormality, such as poor AV node conduction or poor SA node function, may receive an implantable medical device (IMD), such as a pacemaker, to restore a more normal heart rhythm and AV synchrony. Some types of IMDs, such as cardiac pacemakers, implantable cardioverter defibrillators (ICDs), or cardiac resynchronization therapy (CRT) devices, provide therapeutic electrical stimulation to a heart of a patient via electrodes on one or more implantable endocardial, epicardial, or coronary venous leads that are positioned in or adjacent to the heart. The therapeutic electrical stimulation may be delivered to the heart in the form of pulses or shocks for pacing, cardioversion, or defibrillation. In some cases, an IMD may sense intrinsic depolarizations of the heart, and control the delivery of therapeutic stimulation to the heart based on the sensing.

Delivery of therapeutic electrical stimulation to the heart can be useful in addressing cardiac conditions such as ventricular dyssynchrony that may occur in patients. Ventricular dyssynchrony may be described as a lack of synchrony or a difference in the timing of contractions between the ventricles of the heart. Significant differences in timing of contractions can reduce cardiac efficiency. CRT, delivered by an IMD to the heart, may enhance cardiac output by resynchronizing the electromechanical activity of the ventricles of the heart. CRT is sometimes referred to as “triple chamber pacing” because CRT can deliver pacing to the right atrium, right ventricle, and left ventricle.

Cardiac arrhythmias may be treated by delivering electrical shock therapy for cardioverting or defibrillating the heart in addition to cardiac pacing, for example, from an ICD, which may sense a patient's heart rhythm and classify the rhythm according to an arrhythmia detection scheme in order to detect episodes of tachycardia or fibrillation. Arrhythmias detected may include ventricular tachycardia (VT), fast ventricular tachycardia (FVT), ventricular fibrillation (VF), atrial tachycardia (AT) and atrial fibrillation (AT). Anti-tachycardia pacing (ATP), a painless therapy, can be used to treat ventricular tachycardia (VT) to substantially terminate many monomorphic fast rhythms. While ATP is painless, ATP may not deliver effective therapy for all types of VTs. For example, ATP may not be as effective for polymorphic VTs, which has variable morphologies. Polymorphic VTs and ventricular fibrillation (VFs) can be more lethal and may require expeditious treatment by shock.

Dual chamber medical devices are available that include a transvenous atrial lead carrying electrodes that may be placed in the right atrium and a transvenous ventricular lead carrying electrodes that may be placed in the right ventricle via the right atrium. Such dual-chamber medical devices are generally implanted in a subcutaneous pocket and the transvenous leads are tunneled to the subcutaneous pocket. Further, such dual-chamber medical devices may sense atrial electrical signals and ventricular electrical signals and can provide both atrial pacing and ventricular pacing as needed to promote a normal heart rhythm and AV synchrony. Some dual-chamber medical devices can treat both atrial and ventricular arrhythmias.

In some patients, single-chamber devices may adequately address the patient's needs. However, single-chamber devices capable of only single chamber sensing and therapy may not fully address cardiac conduction disease or abnormalities in all patients, for example, those with some forms of AV dyssynchrony or tachycardia. Dual-chamber sensing and/or pacing functions, in addition to ICD functionality in some cases, may be used to restore more normal heart rhythms.

SUMMARY

The techniques of this disclosure generally relate to a delivery catheter that guides an implantable medical device or lead to the correct location in the triangle of Koch region and at an orientation to deliver pacing to the LV using the CS as a physical reference.

In one aspect, the present disclosure provides an implantable medical device delivery system including an elongated element anchorable in the coronary sinus (CS) of a patient's heart. The system also includes a delivery catheter with an elongated body having a first portion defining a first lumen and a second portion defining a second lumen. The first lumen in a first distal end region of the first portion extends along a first axis and the second lumen in a second distal end region of the second portion extends along a second axis forming an angle with the first axis. The second axis points toward the left ventricular (LV) apex of the patient's heart when the anchorable elongated element is advanced through the first lumen into the CS.

In another aspect, the present disclosure provides a delivery catheter including a first portion advanceable into the coronary sinus (CS) of a patient's heart having an elongated body defining a first lumen and an exterior channel. When the first portion is advanced into the CS, a region of the first portion adjacent to the CS ostium of the patient's heart extends along a first axis. The device includes a second portion having an elongated body defining a second lumen and having a laterally-extending protrusion configured to be received into the exterior channel of the first portion to slidably guide the second portion along a length of the first portion. A distal end region of the second portion extends along a second axis when the protrusion is engaged in the channel forming a fixed angle with the first axis such that the second axis points toward the left ventricular (LV) apex of the patient's heart when the first portion is advanced into the CS.

In yet another aspect, the present disclosure provides a method of delivering an implantable medical device that includes advancing a first distal end region of a first portion of a dual-lumen catheter toward the coronary sinus (CS) of a patient's heart. The first portion defines a first lumen and the first distal end region extends along a first axis. The method includes orienting a second distal end region of a second portion of the dual-lumen catheter toward the triangle of Koch region of the patient's heart. The second portion defines a second lumen and the second distal end region extends along a second axis forming an angle with the first axis such that the second axis points toward the left ventricular (LV) apex of the patient's heart when the first distal end region is fully advanced toward the CS.

The details of one or more aspects of the disclosure are set forth in the accompanying drawings and the description below. Other features, objects, and advantages of the techniques described in this disclosure will be apparent from the description and drawings, and from the claims.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a conceptual diagram of an example of a cardiac therapy system including a delivery system to implant an implantable medical device in a patient's heart shown in a cross-sectional view and a separate medical device positioned outside of the patient's heart.

FIG. 2 is a conceptual diagram of an example of intracardiac medical device that may be delivered with the delivery system of FIG. 1 and anatomical structures of the patient's heart.

FIG. 3 is a perspective view of another example of an intracardiac medical device that may be delivered with the delivery system of FIG. 1.

FIG. 4 is a conceptual diagram of a map of a patient's heart in a standard 17 segment view of the left ventricle showing various electrode implantation locations for use with, e.g., the exemplary systems of FIGS. 1-3.

FIGS. 5A-C are conceptual diagrams of one example of the delivery system of FIG. 1.

FIG. 6 is a conceptual diagram of another example of the delivery system of FIG. 1.

FIG. 7 is a flowchart of one example of a method of using the delivery system of FIG. 1.

FIG. 8 is a flowchart of one example of performing, or carrying out, the method of FIG. 7.

FIG. 9 is a flowchart of another example of performing, or carrying out, the method of FIG. 7.

FIG. 10 is a flowchart of yet another example of performing, or carrying out, the method of FIG. 7.

DETAILED DESCRIPTION

This disclosure relates to delivery of implantable medical devices, systems, and methods for ventricle-from-atrium (VfA) cardiac therapy, including single or multiple-chamber pacing (e.g., dual- or triple-chamber pacing), atrioventricular synchronous pacing, asynchronous pacing, triggered pacing, cardiac resynchronization pacing, or tachycardia-related therapy. Although reference is made herein to implantable medical devices (IMDs), such as a pacemaker or ICD, the methods and processes may be used with any medical devices, systems, or methods related to a patient's heart. Various other applications will become apparent to one of skill in the art having the benefit of the present disclosure.

The procedure for locating a VfA device, or lead, in or at the correct implant location and orientation, so as to aim in the correct direction to stimulate the LV endocardial tissue, may be difficult. There are at least two factors to consider for such VfA device placement. First, the catheter tip of the delivery catheter is to be guided to the triangle of Koch between the CS ostium and the tricuspid valve annulus, which is smooth location in which it may be difficult to hold the placement of a catheter due to the instability of the locale. Second, once the catheter is in position, the device must be oriented in the correct plane of tissue to position an electrode in the LV tissue for pacing.

The present disclosure provides a delivery catheter, which may be described as a dual-lumen, or bi-lumen, catheter that may create stability at a target implant region and may also provide the correct angle into the tissue for providing VfA cardiac therapy. In particular, an example of a delivery catheter may guide an implantable medical device or lead to the correct location in the triangle of Koch region and at an orientation to deliver pacing to the LV using the CS as a physical reference. For example, a portion of the delivery catheter or an elongated element extending through the portion into the CS may anchor the delivery catheter based on the orientation of the CS. In one embodiment, one lumen of the delivery catheter may be used to track, or guide, an elongated member into the CS, and another lumen of the delivery catheter may have a bend near the distal end region to angle a device delivered thereby into the tissue in the correct orientation. The lumens may be described as being positioned side-by-side.

Reference will now be made to the drawings, which depict one or more aspects described in this disclosure. However, it will be understood that other aspects not depicted in the drawings fall within the scope of this disclosure. Like numbers used in the figures refer to like components, steps, and the like. However, it will be understood that the use of a reference character to refer to an element in a given figure is not intended to limit the element in another figure labeled with the same reference character. In addition, the use of different reference characters to refer to elements in different figures is not intended to indicate that the differently referenced elements cannot be the same or similar.

Although the present disclosure describes leadless and leaded implantable medical devices, reference is first made to FIG. 1 showing a conceptual diagram of a cardiac therapy system 2 including a leaded medical device 104, which may also be described as an implantable medical lead, that may be configured for single- or dual-chamber therapy and implanted in a patient's heart 8. In some embodiments, the device 104 may be configured for single chamber pacing and may, for example, switch between single chamber and multiple chamber pacing (e.g., dual- or triple-chamber pacing).

The device 104 is shown implanted in the right atrium (RA) of the patient's heart 8 in a target implant region 4. The device 104 may include one or more fixation members (such as fixation members 20 in FIG. 2) that anchor a distal end of the device against the atrial endocardium in a target implant region 4. The target implant region 4 may lie between the Bundle of His 5 and the coronary sinus 3 and may be adjacent the tricuspid valve 6. The device 104 may be described as a ventricle-from-atrium (VfA) device, which may sense or provide therapy to one or both ventricles (e.g., right ventricle, left ventricle, or both ventricles, depending on the circumstances) while being generally disposed in the right atrium. In particular, the device 104 may include a tissue-piercing electrode that may be implanted in the high basal and/or septal region of the left ventricular myocardium of the patient's heart from the triangle of Koch region of the right atrium through the right atrial endocardium and central fibrous body.

Effective delivery of the device 104 to a precise location in the target implant region 4 at a desired orientation may be challenging. A delivery catheter 100 may provide a stable anchoring to the CS to facilitate delivery of the device 104 to the target implant region 4. The stable anchoring may be facilitated by the use of an elongated element 102 that extends through the delivery catheter 100. In some embodiments, the delivery catheter 100 may be described as a dual-lumen catheter. The dual-lumen catheter may include a first portion 101 defining a first lumen and a second portion 103 defining a second lumen, which may be integrally formed from a single piece of material or separately formed. The first portion 101 may extend into the CS, or the first lumen to of the first portion may be used to deliver the elongated element 102 into the CS, for anchoring. A second lumen may be used to deliver the implantable medical device 104, or lead, to the triangle of Koch for implantation. The dual-lumen catheter may be described as being pre-shaped or configured to provide a fixed or deflectable angle between the first lumen and the second lumen, for example, at least at their distal end regions. When the first lumen is aligned to the orientation of the coronary sinus using the elongated element 102 extended into the CS, the second lumen may be oriented and aligned to the triangle of Koch region at an angle that will implant the tissue-piercing electrode of the device 104 into the high basal and/or septal region of the LV myocardium from the triangle of Koch region of the RA through the RA endocardium and central fibrous body. The delivery catheter 100 may be removed after delivery of the device 104.

The device 104 may include one or more dart electrodes 12 having a straight shaft extending from the distal end region of device 104, through the atrial myocardium and the central fibrous body, and into the ventricular myocardium 14 or along the ventricular septum, without perforating entirely through the ventricular endocardial or epicardial surfaces. In other words, the one or more dart electrodes 12 may not pierce through the ventricular wall into the blood volume. The one or more dart electrodes 12 may each carry one or more electrode elements at the distal end region of the shaft for positioning the one or more electrode elements within the ventricular myocardium for sensing ventricular signals and delivering ventricular pulses (e.g., to depolarize the left ventricle to initiate a contraction of the left ventricle). In some examples, the electrode elements at the distal end region of the shaft may include a cathode electrode provided for use in a bipolar electrode pair for pacing and sensing. While the implant region 4 is shown in FIG. 1 to enable one or more electrodes of the one or more dart electrodes 12 to be positioned in the ventricular myocardium, it is recognized that a device having the aspects disclosed herein may be implanted at other locations for multiple-chamber pacing (e.g., dual- or triple-chamber pacing), single-chamber pacing with multiple-chamber sensing, single-chamber pacing and/or sensing, or other clinical therapy and applications as appropriate.

The cardiac therapy system 2 may also include a separate medical device 50 (depicted diagrammatically in FIG. 1), which may be positioned outside the patient's heart 8 (e.g., subcutaneously) and may be operably coupled to the patient's heart 8 to deliver cardiac therapy thereto. In one example, separate medical device 50 may be an extravascular ICD. In some embodiments, an extravascular ICD may include a defibrillation lead with a defibrillation electrode. A therapy vector may exist between the defibrillation electrode on the defibrillation lead and a housing electrode of the ICD. Further, one or more electrodes of the ICD may also be used for sensing electrical signals related to the patient's heart 8. The ICD may be configured to deliver shock therapy including one or more defibrillation or cardioversion shocks. For example, if an arrhythmia is sensed, the ICD may send a pulse via the electrical lead wires to shock the heart and restore its normal rhythm. In some examples, the ICD may deliver shock therapy without placing electrical lead wires within the heart or attaching electrical wires directly to the heart (subcutaneous ICDs). Examples of extravascular, subcutaneous ICDs that may be used with the system 2 described herein may be described in U.S. Pat. No. 9,278,229 (Reinke et al.), issued 8 Mar. 2016, which is incorporated herein by reference in its entirety.

The device 104 and the separate medical device 50 may cooperate to provide cardiac therapy to the patient's heart 8. For example, the device 104 and the separate medical device 50 may be used to detect tachycardia, monitor tachycardia, and/or provide tachycardia-related therapy. For example, the device 104 may communicate with the separate medical device 50 wirelessly to trigger shock therapy using the separate medical device 50. As used herein, “wirelessly” refers to an operative coupling or connection without using a metal conductor connecting the device 104 and the separate medical device 50. In one example, wireless communication may use a distinctive, signaling, or triggering electrical pulse provided by the device 104 that conducts through the patient's tissue and is detectable by the separate medical device 50. In another example, wireless communication may use a communication interface (e.g., an antenna) of the device 104 to provide electromagnetic radiation that propagates through patient's tissue and is detectable, for example, using a communication interface (e.g., an antenna) of the separate medical device 50.

FIG. 2 is a conceptual diagram of a leadless implantable medical device 106, or an intracardiac medical device, and anatomical structures of the patient's heart 8. One or more of the features described with respect to device 106 may also be used with a leaded IMD, such as leaded IMD 104 (FIG. 1). As used herein, “intracardiac” refers to a device configured to be implanted entirely within a patient's heart, for example, to provide cardiac therapy.

The intracardiac device 10 may include a housing 30. The housing 30 may define a hermetically-sealed internal cavity in which internal components of the device 106 reside, such as a sensing circuit, therapy delivery circuit, control circuit, memory, telemetry circuit, other optional sensors, and a power source. The housing 30 may be formed from an electrically conductive material including titanium or titanium alloy, stainless steel, MP35N (a non-magnetic nickel-cobalt-chromium-molybdenum alloy), platinum alloy or other bio-compatible metal or metal alloy. In other examples, the housing 30 may be formed from a non-conductive material including ceramic, glass, sapphire, silicone, polyurethane, epoxy, acetyl co-polymer plastics, polyether ether ketone (PEEK), a liquid crystal polymer, or other biocompatible polymer.

The device 106 may be described being as a leadless implantable medical device. As used herein, “leadless” refers to a device being free of a lead extending out of the patient's heart 8. In other words, a leadless device may have a lead that does not extend from outside of the patient's heart to inside of the patient's heart. Some leadless devices may be introduced through a vein, but once implanted, the device is free of, or may not include, any transvenous lead and may be configured to provide cardiac therapy without using any transvenous lead. A leadless VfA device, in particular, does not use a lead to operably connect to an electrode in the ventricle when a housing of the device is positioned in the atrium. A leadless electrode may be coupled to the housing of the medical device without using a lead between the electrode and the housing.

The housing 30 may be described as extending between a distal end region 32 and a proximal end region 34 in a generally cylindrical shape to facilitate catheter delivery. In other embodiments, the housing 30 may be prismatic or any other shape so as to perform the functionality and utility described herein. The housing 30 may include a delivery tool interface member 26, e.g., at the proximal end 34, for engaging with a delivery tool during implantation of the device 106. For example, the delivery tool interface member 26 may be used while the device 106 is advanced toward the target implant region 4 using the delivery catheter 100 (FIG. 1).

All or a portion of the housing 30 may function as an electrode during cardiac therapy, for example, in sensing and/or pacing. In the example shown, the housing-based electrode 24 is shown to circumscribe a proximal portion of the housing 30. When the housing 30 includes (e.g., is formed from) an electrically conductive material, such as a titanium alloy or other examples listed above, portions of the housing 30 may be electrically insulated by a non-conductive material, such as a coating of parylene, polyurethane, silicone, epoxy, or other biocompatible polymer, leaving one or more discrete areas of conductive material exposed to define the proximal housing-based electrode 24. When the housing 30 includes (e.g., is formed from) a non-conductive material, such as a ceramic, glass, or polymer material, an electrically-conductive coating or layer, such as a titanium, platinum, stainless steel, or alloys thereof, may be applied to one or more discrete areas of the housing 30 to form the proximal housing-based electrode 24. In other examples, the proximal housing-based electrode 24 may be a component, such as a ring electrode, that is mounted or assembled onto the housing 30. The proximal housing-based electrode 24 may be electrically coupled to internal circuitry of the device 106, e.g., via the electrically-conductive housing 30 or an electrical conductor when the housing 30 includes a non-conductive material.

In the example shown, the housing-based electrode 24 is located nearer to the housing proximal end region 34 than the housing distal end region 32 and may, therefore, be described as being a proximal housing-based electrode. In other examples, however, the housing-based electrode 24 may be located at other positions along the housing 30, e.g., relatively more distally than the position shown in FIG. 2.

At the distal end region 32, the device 106 may include a distal fixation and electrode assembly 36, which may include one or more fixation members 20, in addition to one or more dart electrodes 12 of equal or unequal length. The device 106 as depicted includes a single dart electrode 12 that may include a shaft 40 extending distally away from the housing distal end region 32 and may include one or more electrode elements, such as a tip electrode element 42 at or near the free, distal end region of the shaft 40. The tip electrode element 42 may have a conical or hemi-spherical distal tip with a relatively narrow tip diameter (e.g., less than about 1 millimeter (mm)) for penetrating into and through tissue layers without using a sharpened tip or needle-like tip having sharpened or beveled edges.

The shaft 40 of the dart electrode 12 may be a normally straight member and may be rigid. In other embodiments, the shaft 40 may be described as being relatively stiff but still possessing limited flexibility in lateral directions (e.g., resilient or semi-rigid). Further, the shaft 40 may be non-rigid to allow some lateral flexing with heart motion. However, in a relaxed state, when not subjected to any external forces, the shaft 40 may maintain a straight position as shown to hold the tip electrode element 42 spaced apart from the housing distal end region 32 at least by the length or height 47 of the shaft 40. The dart electrode 12 may be configured to pierce through one or more tissue layers to position the tip electrode element 42 within a desired tissue layer, e.g., the ventricular myocardium. As such, the length or height 47 of the shaft 40 may correspond to the expected pacing site depth, and the shaft may have a relatively high compressive-strength along its longitudinal axis to resist bending in a lateral or radial direction when pressed against the implant region 4. If a second dart electrode 12 is employed, its length or height may be unequal to the expected pacing site depth and may be configured to act as an indifferent electrode for delivery of pacing energy to the tissue. A longitudinal axial force may be applied against the tip electrode element 42, e.g., by applying longitudinal “pushing” force to the proximal end 34 of the housing 30, to advance the dart electrode 12 into the tissue within target implant region 4. The shaft 40 may be longitudinally non-compressive. Further, the shaft 40 may be elastically deformable in lateral or radial directions when subjected to lateral or radial forces to allow temporary flexing, e.g., with tissue motion, but may return to its normally straight position when lateral forces diminish. When the shaft 40 is not exposed to any external force, or to only a force along its longitudinal central axis, the shaft 40 may retain a straight, linear position as shown.

The one or more fixation members 20 may be described as one or more “tines” having a normally-curved position. The tines may be held in a distally extended position within a delivery tool. The distal tips of tines may penetrate the heart tissue to a limited depth before elastically curving back proximally into the normally curved position (shown) upon release from the delivery tool. Further, the fixation members 20 may include one or more aspects described in, for example, U.S. Pat. No. 9,675,579 (Grubac et al.), issued 13 Jun. 2017, and U.S. Pat. No. 9,119,959 (Rys et al.), issued 1 Sep. 2015, each of which is incorporated herein by reference in its entirety.

In some examples, the distal fixation and electrode assembly 36 includes a distal housing-based electrode 22. In the case of using the device 106 as a pacemaker for multiple-chamber pacing (e.g., dual- or triple-chamber pacing) and sensing, the tip electrode element 42 may be used as a cathode electrode paired with the proximal housing-based electrode 24 serving as a return anode electrode. Alternatively, the distal housing-based electrode 22 may serve as a return anode electrode paired with tip electrode element 42 for sensing ventricular signals and delivering ventricular pacing pulses. In other examples, the distal housing-based electrode 22 may be a cathode electrode for sensing atrial signals and delivering pacing pulses to the atrial myocardium in the target implant region 4. When the distal housing-based electrode 22 serves as an atrial cathode electrode, the proximal housing-based electrode 24 may serve as the return anode paired with the tip electrode element 42 for ventricular pacing and sensing and as the return anode paired with the distal housing-based electrode 22 for atrial pacing and sensing.

As shown in this illustration, the target implant region 4 in some pacing applications is along the atrial endocardium 18, generally inferior to the AV node 15 and the His bundle 5. The dart electrode 42 may define the length or height 47 of the shaft 40 for penetrating through the atrial endocardium 18 in the target implant region 4, through the central fibrous body 16, and into the ventricular myocardium 14 without perforating through the ventricular endocardial surface 17. When the length or height 47 of the dart electrode 12 is fully advanced into the target implant region 4, the tip electrode element 42 may rest, or be positioned, within the ventricular myocardium 14, and the distal housing-based electrode 22 may be positioned in intimate contact with or close proximity to the atrial endocardium 18. The dart electrode 12 may have a total combined length or height 47 of tip electrode element 42 and shaft 40 from about 3 mm to about 8 mm in various examples. The diameter of the shaft 40 may be less than about 2 mm, and may be about 1 mm or less, or even about 0.6 mm or less.

The device 106 may include a motion detector 11 within the housing 30. The motion detector 11 may be used to monitor mechanical activity, such as atrial mechanical activity (e.g., an atrial contraction) and/or ventricular mechanical activity (e.g., a ventricular contraction). In some embodiments, the motion detector 11 may be used to detect right atrial mechanical activity. A non-limiting example of a motion detector 11 includes an accelerometer. In some embodiments, the mechanical activity detected by the motion detector 11 may be used to supplement or replace electrical activity detected by one or more of the electrodes of the device 106. For example, the motion detector 11 may be used in addition to, or as an alternative to, the proximal housing-based electrode 24.

The motion detector 11 may also be used for rate response detection or to provide a rate-responsive 1 MB. Various techniques related to rate response may be described in U.S. Pat. No. 5,154,170 (Bennett et al.), issued Oct. 13, 1992, entitled “Optimization for rate responsive cardiac pacemaker,” and U.S. Pat. No. 5,562,111 (Yerich et al.), issued Oct. 8, 1996, entitled “Method and apparatus for rate-responsive cardiac pacing,” each of which is incorporated herein by reference in its entirety.

FIG. 3 is a three-dimensional perspective view of another example of a leadless implantable medical device 110, or intracardiac medical device, that may be configured for single- or multiple-chamber cardiac therapy (e.g., dual- or triple-chamber cardiac therapy). One or more of the features described with respect to device 110 may also be used with a leaded IMD, such as leaded 1 MB 104 (FIG. 1).

The device 110 may include a housing 130 having, or defining, an outer sidewall 135, shown as a cylindrical outer sidewall, extending from a housing distal end region 132 to a housing proximal end region 134. The housing 130 may enclose electronic circuitry configured to perform single or multiple chamber cardiac therapy, including atrial and ventricular cardiac electrical signal sensing and pacing the atrial and ventricular chambers. Delivery tool interface member 126 is shown on the housing proximal end region 134.

A distal fixation and electrode assembly 136 may be coupled to the housing distal end region 132. The distal fixation and electrode assembly 136 may include an electrically-insulative distal member 172 coupled to the housing distal end region 132. The tissue-piercing electrode 112 extends away from the housing distal end region 132, and multiple non-tissue-piercing electrodes 122 may be coupled directly to the insulative distal member 172. The tissue-piercing electrode 112 extends in a longitudinal direction away from the housing distal end region 132 and may be coaxial with the longitudinal center axis 131 of the housing 130.

The tissue-piercing distal electrode 112 may include an electrically-insulated shaft 140 and a tip electrode element 142. In some examples, the tissue-piercing distal electrode 112 also functions as a fixation member and may include a helical shaft 140 and a distal cathode tip electrode element 142. The helical shaft 140 may extend from a shaft distal end region 143 to a shaft proximal end region 141, which may be directly coupled to the insulative distal member 172. The helical shaft 140 may be coated with an electrically insulating material, e.g., parylene or other examples listed herein, to avoid sensing or stimulation of cardiac tissue along the shaft length. The tip electrode element 142 is at the shaft distal end region 143 and may serve as a cathode electrode for delivering ventricular pacing pulses and sensing ventricular electrical signals using the proximal housing-based electrode 124 as a return anode when the tip electrode element 142 is advanced into ventricular tissue. The proximal housing-based electrode 124 may be a ring electrode circumscribing the housing 130 and may be defined by an uninsulated portion of the longitudinal sidewall 135. Other portions of the housing 130 not serving as an electrode may be coated with an electrically insulating material as described above in conjunction with FIG. 2.

Using two or more tissue-piercing electrodes (e.g., of any type) penetrating into the LV myocardium may be used for localized pacing capture and may mitigate ventricular pacing spikes affecting capturing atrial tissue. In some embodiments, multiple tissue-piercing electrodes may include two or more of a dart-type electrode (e.g., electrode 12 of FIGS. 1-2) and a helical-type electrode (e.g., electrode 112). Non-limiting examples of multiple tissue-piercing electrodes include two dart electrodes, a helix electrode with a dart electrode extending therethrough (e.g., through the center), or dual intertwined helixes. Multiple tissue-piercing electrodes may also be used for bipolar or multi-polar pacing.

In some embodiments, one or more tissue-piercing electrodes (e.g., of any type) that penetrate into the LV myocardium may be multi-polar tissue-piercing electrodes. A multi-polar tissue-piercing electrode may include one or more electrically active and electrically separate elements, which may enable bipolar or multi-polar pacing from one or more tissue-piercing electrodes.

Multiple non-tissue-piercing electrodes 122 may be provided along a periphery of the insulative distal member 172 (e.g., peripheral to the tissue-piercing electrode 1120. The insulative distal member 172 may define a distal-facing surface 138 of the device 110 and a circumferential surface 139 that circumscribes the device 110 adjacent to the housing longitudinal sidewall 135. Non-tissue-piercing electrodes 122 may be formed of an electrically conductive material, such as titanium, platinum, iridium, or alloys thereof. In the illustrated embodiment, six non-tissue-piercing electrodes 122 are spaced apart radially at equal distances along the outer periphery of the insulative distal member 172. However, two or more non-tissue-piercing electrodes 122 may be provided in some embodiments.

Non-tissue-piercing electrodes 122 may be discrete components each retained within a respective recess 174 in the insulative member 172 sized and shaped to mate with the non-tissue-piercing electrode 122. In other examples, the non-tissue-piercing electrodes 122 may each be an uninsulated, exposed portion of a unitary member mounted within or on the insulative distal member 172. Intervening portions of the unitary member not functioning as an electrode may be insulated by the insulative distal member 172 or, if exposed to the surrounding environment, may be coated with an electrically insulating coating, e.g., parylene, polyurethane, silicone, epoxy, or other insulating coating.

When the tissue-piercing electrode 112 is advanced into cardiac tissue, at least one non-tissue-piercing electrode 122 may be positioned against, in intimate contact with, or in operative proximity to, a cardiac tissue surface for delivering pulses and/or sensing cardiac electrical signals produced by the patient's heart. For example, one or more non-tissue-piercing electrodes 122 may be positioned in contact with right atrial endocardial tissue for pacing and sensing in the atrium when the tissue-piercing electrode 112 is advanced into the atrial tissue and through the central fibrous body until the distal tip electrode element 142 is positioned in direct contact with ventricular tissue, e.g., ventricular myocardium and/or a portion of the ventricular conduction system.

Non-tissue-piercing electrodes 122 may be coupled to a therapy delivery circuit and a sensing circuit enclosed by the housing 130 to function collectively as a cathode electrode for delivering atrial pacing pulses and for sensing atrial electrical signals (e.g., P-waves) in combination with the proximal housing-based electrode 124 as a return anode. Switching circuitry included in the sensing circuit may be activated under the control of the control circuit to couple one or more of the non-tissue-piercing electrodes to the atrial sensing channel. Distal, non-tissue-piercing electrodes 122 may be electrically isolated from each other so that each individual one of the electrodes 122 may be individually selected by switching circuitry included in the therapy delivery circuit to serve alone or in a combination with two or more of the electrodes 122 as an atrial cathode electrode. Switching circuitry included in the therapy delivery circuit may be activated under the control of the control circuit to couple one or more of the non-tissue-piercing electrodes 122 to the atrial pacing circuit. Two or more of the non-tissue-piercing electrodes 122 may be selected at a time to operate as a multi-point atrial cathode electrode.

Certain non-tissue-piercing electrodes 122 selected for atrial pacing and/or atrial sensing may be selected based on atrial capture threshold tests, electrode impedance, P-wave signal strength in the cardiac electrical signal, or other factors. For example, a single one or any combination of two or more individual non-tissue-piercing electrodes 122 functioning as a cathode electrode that provides an optimal combination of a low pacing capture threshold amplitude and relatively high electrode-impedance may be selected to achieve reliable atrial pacing using minimal current drain from the power source.

In some instances, the distal-facing surface 138 may uniformly contact the atrial endocardial surface when the tissue-piercing electrode 112 anchors the housing 130 at the implant site. In that case, all the electrodes 122 may be selected together to form the atrial cathode. Alternatively, every other one of the electrodes 122 may be selected together to form a multi-point atrial cathode having a higher electrical impedance that is still uniformly distributed along the distal-facing surface 138. Alternatively, a subset of one or more electrodes 122 along one side of the insulative distal member 172 may be selected to provide pacing at a desired site that achieves the lowest pacing capture threshold due to the relative location of the electrodes 122 to the atrial tissue being paced.

In other instances, the distal-facing surface 138 may be oriented at an angle relative to the adjacent endocardial surface depending on the positioning and orientation at which the tissue-piercing electrode 112 enters the cardiac tissue. In this situation, one or more of the non-tissue-piercing electrodes 122 may be positioned in closer contact with the adjacent endocardial tissue than other non-tissue-piercing electrodes 122, which may be angled away from the endocardial surface. By providing multiple non-tissue-piercing electrodes along the periphery of the insulative distal member 172, the angle of the tissue-piercing electrode 112 and the housing distal end region 132 relative to the cardiac surface, e.g., the right atrial endocardial surface, may not be required to be substantially parallel. Anatomical and positional differences may cause the distal-facing surface 138 to be angled or oblique to the endocardial surface, however, multiple non-tissue-piercing electrodes 122 distributed along the periphery of the insulative distal member 172 may increase the likelihood of “good” contact between one or more electrodes 122 and the adjacent cardiac tissue to promote acceptable pacing thresholds and reliable cardiac event sensing using at least a subset of multiple electrodes 122. Contact or fixation circumferentially along the entire periphery of the insulative distal member 172 may not be required.

The non-tissue-piercing electrodes 122 are shown to each include a first portion 122a extending along the distal-facing surface 138 and a second portion 122b extending along the circumferential surface 139. The first portion 122a and the second portion 122b may be continuous exposed surfaces such that the active electrode surface wraps around a peripheral edge 176 of the insulative distal member 172 that joins the distal facing surface 138 and the circumferential surface 139. The non-tissue-piercing electrodes 122 may include one or more of the electrodes along the distal-facing surface 138, one or more electrodes along the circumferential surface 139, one or more electrodes each extending along both of the distal-facing surface 138 and the circumferential surface 139, or any combination thereof. The exposed surface of each of the non-tissue-piercing electrodes 122 may be flush with respective distal-facing surfaces 138 and/or circumferential surfaces. In other examples, each of the non-tissue-piercing electrodes 122 may have a raised surface that protrudes from the insulative distal member 172. Any raised surface of the electrodes 122, however, may define a smooth or rounded, non-tissue-piercing surface.

The distal fixation and electrode assembly 136 may seal the distal end region of the housing 130 and may provide a foundation on which the electrodes 122 are mounted. The electrodes 122 may be referred to as housing-based electrodes. The electrodes 122 may not be not carried by a shaft or other extension that extends the active electrode portion away from the housing 130, like the distal tip electrode element 142 residing at the distal tip of the helical shaft 140 extending away from the housing 130. Other examples of non-tissue-piercing electrodes presented herein that are coupled to a distal-facing surface and/or a circumferential surface of an insulative distal member include the distal housing-based ring electrode 22 (FIG. 2), the distal housing-based ring electrode extending circumferentially around the assembly 36 (FIG. 2), button electrodes, other housing-based electrodes, and other circumferential ring electrodes. Any non-tissue-piercing electrodes directly coupled to a distal insulative member, peripherally to a central tissue-piercing electrode, may be provided to function individually, collectively, or in any combination as a cathode electrode for delivering pacing pulses to adjacent cardiac tissue. When a ring electrode, such as the distal ring electrode 22 and/or a circumferential ring electrode, is provided, portions of the ring electrode may be electrically insulated by a coating to provide multiple distributed non-tissue-piercing electrodes along the distal-facing surface and/or the circumferential surface of the insulative distal member.

The non-tissue-piercing electrodes 122 and other examples listed above are expected to provide more reliable and effective atrial pacing and sensing than a tissue-piercing electrode provided along the distal fixation and electrode assembly 136. The atrial chamber walls are relatively thin compared to ventricular chamber walls. A tissue-piercing atrial cathode electrode may extend too deep within the atrial tissue leading to inadvertent sustained or intermittent capture of ventricular tissue. A tissue-piercing atrial cathode electrode may lead to interference with sensing atrial signals due to ventricular signals having a larger signal strength in the cardiac electrical signal received via tissue-piercing atrial cathode electrodes that are in closer physical proximity to the ventricular tissue. The tissue-piercing electrode 112 may be securely anchored into ventricular tissue for stabilizing the implant position of the device 110 and providing reasonable certainty that the tip electrode element 142 is sensing and pacing in ventricular tissue while the non-tissue-piercing electrodes 122 are reliably pacing and sensing in the atrium. When the device 110 is implanted in the target implant region 4, e.g., as shown in FIG. 1 the ventricular septum, the tip electrode element 142 may reach left ventricular tissue for pacing of the left ventricle while the non-tissue-piercing electrodes 122 provide pacing and sensing in the right atrium. The tissue-piercing electrode 112 may be in the range of about 4 to about 8 mm in length from the distal-facing surface 138 to reach left ventricular tissue. In some instances, the device 110 may achieve four-chamber pacing by delivering atrial pacing pulses from the atrial pacing circuit via the non-tissue-piercing electrodes 122 in the target implant region 4 to achieve bi-atrial (right and left atrial) capture and by delivering ventricular pacing pulses from the ventricular pacing circuit via the tip electrode element 142 advanced into ventricular tissue from the target implant region 4 to achieve biventricular (right and left ventricular) capture.

One or more of the components, such as controllers, circuitry, accelerometers, or sensors, described herein may include a processor, such as a central processing unit (CPU), computer, logic array, or other device capable of directing data coming into or out of the medical device. The controller may include one or more computing devices or processing circuitry having memory, processing, and communication hardware. The controller may include circuitry used to couple various components of the controller together or with other components operably coupled to the controller. The functions of the controller may be performed by hardware and/or as computer instructions on a non-transient computer readable storage medium.

The processor of the controller may include any one or more of a microprocessor, a microcontroller, a digital signal processor (DSP), an application specific integrated circuit (ASIC), a field-programmable gate array (FPGA), and/or equivalent discrete or integrated logic circuitry. In some examples, the processor may include multiple components, such as any combination of one or more microprocessors, one or more controllers, one or more DSPs, one or more ASICs, and/or one or more FPGAs, as well as other discrete or integrated logic circuitry. The functions attributed to the controller or processor herein may be embodied as software, firmware, hardware, or any combination thereof. While described herein as a processor-based system, an alternative controller could utilize other components such as relays and timers to achieve the desired results, either alone or in combination with a microprocessor-based system.

In one or more embodiments, the exemplary systems, methods, and other functionality may be implemented using one or more computer programs using a computing apparatus, which may include one or more processors and/or memory. Program code and/or logic described herein may be applied to input data/information to perform functionality described herein and generate desired output data/information. The output data/information may be applied as an input to one or more other devices and/or methods as described herein or as would be applied in a known fashion. In view of the above, it will be readily apparent that the controller functionality as described herein may be implemented in any manner known to one skilled in the art

FIG. 4 is a two-dimensional (2D) ventricular map 60 of a patient's heart (e.g., a top-down view) showing the left ventricle 62 in a standard 17 segment view and the right ventricle 64. The map 60 includes a plurality of areas 68 corresponding to different regions of a human heart. As illustrated, the areas 68 are numerically labeled 1-17 (which, e.g., correspond to a standard 17 segment model of a human heart, correspond to 17 segments of the left ventricle of a human heart, etc.). Areas 68 of the map 60 may include basal anterior area 1, basal anteroseptal area 2, basal inferoseptal area 3, basal inferior area 4, basal inferolateral area 5, basal anterolateral area 6, mid-anterior area 7, mid-anteroseptal area 8, mid-inferoseptal area 9, mid-inferior area 10, mid-inferolateral area 11, mid-anterolateral area 12, apical anterior area 13, apical septal area 14, apical inferior area 15, apical lateral area 16, and apex area 17. The inferoseptal and anteroseptal areas of the right ventricle 64 are also illustrated, as well as the right bunch branch (RBB) and left bundle branch (LBB).

In some embodiments, any of the tissue-piercing electrodes of the present disclosure may be implanted in the basal and/or septal region of the left ventricular myocardium of the patient's heart. In particular, the tissue-piercing electrode may be implanted from the triangle of Koch region of the right atrium through the right atrial endocardium and central fibrous body.

Once implanted, the tissue-piercing electrode may be positioned in the target implant region 4 (FIG. 1), such as the basal and/or septal region of the left ventricular myocardium. With reference to map 60, the basal region includes one or more of the basal anterior area 1, basal anteroseptal area 2, basal inferoseptal area 3, basal inferior area 4, mid-anterior area 7, mid-anteroseptal area 8, mid-inferoseptal area 9, and mid-inferior area 10. With reference to map 60, the septal region includes one or more of the basal anteroseptal area 2, basal anteroseptal area 3, mid-anteroseptal area 8, mid-inferoseptal area 9, and apical septal area 14.

In some embodiments, the tissue-piercing electrode may be positioned in the basal septal region of the left ventricular myocardium when implanted. The basal septal region may include one or more of the basal anteroseptal area 2, basal inferoseptal area 3, mid-anteroseptal area 8, and mid-inferoseptal area 9.

In some embodiments, the tissue-piercing electrode may be positioned in the high inferior/posterior basal septal region of the left ventricular myocardium when implanted. The high inferior/posterior basal septal region of the left ventricular myocardium may include a portion of at least one of the basal inferoseptal area 3 and mid-inferoseptal area 9. For example, the high inferior/posterior basal septal region may include region 66 illustrated generally as a dashed-line boundary. As shown, the dashed line boundary represents an approximation of about where the high inferior/posterior basal septal region and may take somewhat different shape or size depending on the particular application. Without being bound by any particular theory, intraventricular synchronous pacing and/or activation may result from stimulating the high septal ventricular myocardium due to functional electrical coupling between the subendocardial Purkinje fibers and the ventricular myocardium.

FIGS. 5A-C show various views of one example of an implementation of the delivery catheter 100 (FIG. 1) that may be used with the elongated element 102. FIG. 5A is a side view showing a delivery catheter 200 that may be used with the elongated element 102. FIG. 5B is an overhead view showing the delivery catheter 200. FIG. 5C is a cross-sectional view along line C-C shown in FIG. 5B.

The elongated element 102 may be any suitable device for insertion into the CS. For example, the elongated element 102 may be a guidewire or a catheter. In some embodiments, the elongated element 102 may be steerable.

Further, the elongated element 102 may be anchorable in the CS. Being anchorable in the CS means the elongated element 102 includes any suitable mechanism for retaining the elongated element within the CS for any period of time. In some embodiments, the elongated element 102 may include an anchorable balloon or an anchorable side helix to facilitate stable anchoring in the CS after insertion of the elongated element into the CS, which may provide a reliable reference for delivering a device to the target implant region 4 (FIG. 1). The elongated element 102 may be inserted any suitable distance into the CS to facilitate the use of the elongated element as a physical reference. The elongated element 102 may remain in the CS or be removed after implanting the device at the target implant region 4.

The elongated element 102 may provide other functionality in addition to providing a physical reference to the CS. In some embodiments, the elongated element 102 may remain in the CS and be used as part of the cardiac therapy system 2 (FIG. 1). For example, the elongated element 102 may include one or more electrodes to facilitate cardiac therapy. In some embodiments, the elongated element 102 may be described as being a therapy catheter, such as an electrophysiology (EP) catheter, used for sensing or pacing. For example, an EP catheter may be used for assessing electrical patterns in the heart and then ablating.

The delivery catheter 200 includes an elongated body including a first portion 202 and a second portion 204, which may be integrally formed from a single piece of material or separately formed and coupled together. The first portion 202 and the second portion 204 may extend from a proximal region 210 to a respective first distal end region 206 and a respective second distal end region 208. As illustrated, the proximal region 210 may represent a proximal end region of the delivery catheter 200 or an intermediate region that is not a proximal end region of the delivery catheter 200. The delivery catheter 200 may be any suitable length to facilitate the techniques of the present disclosure. The first portion 202 and the second portion 204 may each extend longitudinally adjacent to one another, or side-by-side.

Each portion may define a lumen. A first lumen 212 defined by the first portion 202 may extend from the proximal region 210 to the first distal end region 206. A second lumen 214 defined by the second portion 204 may extend from the proximal region 210 to the second distal end region 208.

The first lumen 212 in the first distal end region 206 may be described as extending along a first axis 216. The second lumen 214 in the second distal end region 208 may be described as extending along a second axis 218. The first axis 216 and the second axis 218 form, or define, an angle 220 such that the second axis points toward the LV apex of the patient's heart when the first axis points into the CS. For example, the second axis may point toward the LV apex when the elongated element 102 is advanced through the first lumen 212 at least partially along the first axis 216 and inserted into and optionally anchored in the CS. A device advanced through the second lumen 214 may be directed to an implantation site in the triangle of Koch region when the elongated element 102 is advanced through the first lumen 212 into the CS and the second axis 218 points to the LV apex.

Any suitable angle 220 may be used. The angle 220 may depend on the physiology of the particular patient. In some embodiments, the angle 220 may be at least about 30, 40, 50, 60, or even 70 degrees. In some embodiments, the angle 220 may be at most about 110, 100, 90, 80, or even 70 degrees. For example, the angle 200 may be in a range from about 50 degrees to about 90 degrees. As used herein, “at most” may be used interchangeably with “less than or equal to,” and “at least” may be used interchangeably with “greater than or equal to.”

In one or more embodiments, a different angle may be defined between a first vector perpendicular to the CS ostium of the patient's heart and a second vector from the CS ostium to the LV apex, which may be at least about 30, 40, 50, 70, or even 70 degrees or at most about 110, 100, 90, 80, or even 70 degrees.

In the illustrated embodiment, the proximal region 210 of the second portion 204 is aligned with the first axis 216 and the second distal end region 208 is aligned to the second axis 218. A curved region 222 of the second portion 204 may be defined between the second distal end region 208 and the proximal region 210. The curved region 222 provides a transition between the proximal region 210 and the distal end region, which may be more gradual than illustrated in some embodiments. The first portion 202 may extend relatively linearly along the first axis 216 from the proximal region 210 to the first distal end region 206.

In some embodiments, the second distal end region 208 may also be curved. The alignment of the second distal end region 208 may be defined by the most distal segment of the distal end region or, in particular, the orientation of the medical device extending through the second lumen 214 in the distal end region.

The angle 220 may be described as fixed or deflectable (e.g., resilient). When the angle 220 is deflectable, any suitable mechanism may be used to control, define, or change the angle. For example, in some embodiments, a pull wire may be used to define a deflectable angle 220. In general, the delivery catheter 200 may be formed of any suitable flexible or semi-flexible material for delivery of a device to the patient's heart. In some embodiments, the angle 220 may be defined as a fixed angle when the material used to form some or all of the delivery catheter 200 is sufficiently stiff to prevent deflection away from the target implant region 4 during delivery. The second distal end region 208 or the curved region 222 of the second portion 204 may be formed of the same or different material than the remainder of the second portion, such as the proximal region 210, or than the first portion 202. In some embodiments, the second distal end region 208 or the curved region 222 may be formed of a stiffer material than the proximal region 210 or the first portion 202 (e.g., having a higher Shore durometer). For example, the second distal end region 208 or the curved region 222 may be formed of about a 55D material and the proximal region 210 or the first portion 202 may be formed of about a 35D or 40D material.

In some embodiments, the second portion 204 may include a braided structure to define the second lumen 214 to facilitate shape retention. In other embodiments, the second portion 204 may use a larger wall thickness than the first portion 202 to facilitate shape retention.

Any suitable technique may be used to form the delivery catheter 200. In some embodiments, the delivery catheter 200 may be made of a single extrusion. In other embodiments, the delivery catheter 200 may be made using three-dimensional (3D) machine printing. Any suitable material may be used to form the delivery catheter 200, such as an elastomer. Non-limiting examples of materials that may be used to form the delivery catheter 200 include one or more of polyether block amide (such as PEBAX), polyurethane, or a nylon.

The angled or curved regions of the second portion 204 may be straightened while guiding the delivery catheter 200 to the patient's heart. In some embodiments, a dilator that tracks over a guidewire may be inserted into the second lumen 214 and into the curved region 222 and the second distal end region 208 to straighten the second portion 204. Once the second distal end region 208 reaches the patient's heart, the dilator and the guidewire may be retracted and removed to allow the second portion 204 to take shape and form the angle 220 with the first portion 202.

In some embodiments, the first distal end region 206 may extend into the CS (e.g., as opposed to merely guiding the elongated element 102 into the CS). In the illustrated embodiment, the first portion 202 extends more distally than the second portion 204 such that the first distal end region 206 is more distal than the second distal end region 208 along the first axis 216, which may facilitate insertion and anchoring in the CS. The first portion 202 may extend any suitable amount beyond the second portion 204 to facilitate insertion and anchoring in the CS. For example, the first portion 202 may extend at least one inch or may extend at most two inches beyond the second portion 204.

In other embodiments, the first distal end region 206 may extend toward the CS but may not extend into the CS. In one embodiment, the first distal end region 206 may extend no more distally than the second distal end region 208 or the curved region 222.

The delivery catheter 200 may be a passive or active device. In the illustrated embodiment, the delivery catheter 200 may be described as an active device including one or more electrodes 224. The electrodes 224 may be coupled to the second distal end region 208 of the second portion 204 and used to map atrial activation prior to implanting the device in the target implant region 4. The one or more electrodes 224 may be electrically coupled to a proximal end of the delivery catheter 200 using conductors (not shown) extending through the proximal region 210. In the illustrated embodiment, four electrodes 224 are arranged along a distal face of the second portion 204 around an opening 226 at the end of the second lumen 214. The electrodes 224 may be placed against the triangle of Koch region of the RA to map atrial activation before a device is implanted from the second lumen 214 through the opening 226.

The first lumen 212 and the second lumen 214 may be the same or a different size to accommodate various types of devices. As shown in FIG. 5C, the first lumen 212 may define a first width 232 and the second lumen 214 may define a second width 234. In some embodiments, one or both of the first width 232 and the second width 234 may be described as a first diameter and a second diameter, respectively. As illustrated in FIG. 5C, in some embodiments, the second width 234 may be greater than the first width 232. For example, the first width 232 may be sized to accommodate a guidewire (for example, an inner diameter to accommodate a 0.038-inch guidewire), and the second width 234 may be sized to accommodate a pacing lead (for example, an inner diameter to accommodate a 7 French lead). In other embodiments, the first width 232 and the second width 234 may be the same or similar (for example, see FIG. 6), for example, when configured to insert a catheter and a similarly sized lead into the respective lumens.

FIG. 6 shows a cross-sectional view of another example of an implementation of the delivery catheter 100 (FIG. 1) including an interlocking assembly. The delivery catheter 300 may be similar to the delivery catheter 200 (FIGS. 5A-C) in many respects except that delivery catheter 300 may include an interlocking assembly including an exterior channel 342 defined in the first portion 302 and a protrusion 344 extending laterally from the second portion 304 configured to be received into the channel. The channel 342 may slidably guide the second portion 304 along a length of the first portion 302. The interlocking assembly may allow the first portion 302 and the second portion 304 to be translatable relative to one another. In some embodiments, the first portion 302 may be inserted independently from the second portion 304. In other embodiments, the channel 342 may be defined in the second portion 304, and the protrusion 344 may be extend laterally from the first portion 302.

As used herein with reference to delivery catheters, the term “lateral” refers to a direction away from a longitudinal axis, such as the first axis defined by the first portion 302 or the second axis defined by the second portion 304. In some embodiments, lateral may be a direction that is orthogonal to a longitudinal axis.

The channel 342 and the complementary protrusion 344 may have any suitable depth and complementary height, respectively, to facilitate guidance. In some embodiments, the depth or height may be at least about 0.5, 1, 1.5, or even 2 mm. In some embodiments, the depth or height may be at most about 3, 2.5, 2, 1.5, or even 1 mm. For example, the depth or height may be in a range from about 1 mm to about 2 mm.

The channel 342 may extend any suitable length along the first portion 302. In some embodiments, the channel 342 extends along the entire length of the first portion 302. In some embodiments, the channel 342 may include a distal end that stops short of a distal end of the first portion 302.

The protrusion 344 may extend any suitable length along the second portion 304. In some embodiments, the protrusion 344 is disposed at one or more discrete locations on the elongated body of the second portion 304. For example, each protrusion 344 may have a length that is at most about 1, 2, 3, or even 4 centimeters (cm) along a length of the second portion 304. In one embodiment, the protrusion 344 is disposed at only one discrete location. In other embodiments, the protrusion 344 extends along a greater length of the second portion 304. For example, the protrusion 344 may have a length that is at least about 1, 2, 3, or even 4 cm up to the entire length of the second portion 304. The protrusion 344 may extend continuously or discretely.

The protrusion 344 may be positioned at any suitable location along the second portion 304. In some embodiments, the discrete protrusion 344 may be positioned on the distal end region, the curved region, the proximal region, a non-curved region, or between any of these regions.

FIG. 7 is a flow diagram showing one example of a method 400 of using a delivery catheter of the present disclosure. The method 400 may include advancing a first distal end region of the delivery catheter, or dual-lumen catheter, toward the CS 402. In some embodiments, the first distal end region may be inserted into the CS. The method 400 may also include orienting a second distal end region of the delivery catheter toward the triangle of Koch region 404. Orienting the delivery catheter may involve torqueing to rotate the second portion around the first portion until, for example, the end of the second portion is pointed toward the LV apex when the first distal end region is fully advanced toward the CS. As used herein relative to delivery catheters, the term “torqueing” refers to applying a rotational force, or torque, to the delivery catheter. The method 400 may also include implanting a medical device through the delivery catheter and into the triangle of Koch region 406. In some embodiments, an implantable medical device may be advanced through a second lumen of the delivery catheter extending through the second distal end region. The implantable medical device may be fixed to an implantation site, or target implant region, in the triangle of Koch.

In general, the delivery catheter may be advanced toward the CS over an elongated element, such as a guidewire or another catheter, using a first lumen that extends through the first distal end region of the delivery catheter.

FIG. 8 is a flow diagram showing one example of a method 410 of using a guidewire for the elongated element and an integrally formed delivery-catheter having a first lumen and a second lumen. The method 410 may include advancing a cannulation catheter into the CS 412. In particular, the cannulation catheter may be inserted over a guidewire into the subclavian vein and traverse through the superior vena cava (SVC) to enter the RA and then used to cannulate the CS. The guidewire may be advanced into the CS through the cannulation catheter.

In some embodiments, the guidewire may be anchored in the CS. For example, the guidewire may be advanced more than about 1, 2, 3, 4, 5, or even 6 cm into the CS and even into the great cardiac vein (GCV) to anchor the guidewire in the CS. The method 410 may include removing the cannulation catheter and leaving guidewire in place 414.

The method 410 may also include advancing the delivery catheter, or dual-lumen catheter, over the guidewire toward the CS using the first lumen of the delivery catheter 416. The delivery catheter may be tracked along the guidewire until the delivery catheter prevents further advancement. For example, a portion forming the second lumen may be impeded from further advancement by the CS ostium.

The method 410 may include orienting the second lumen of the delivery catheter toward the triangle of Koch region of the patient's heart 418. In some embodiments, the delivery catheter is torqued so that the second portion of the delivery catheter defining the second lumen, which may have a fixed or deflectable curve, comes into contact with tissue in the target implant location in the triangle of Koch region.

The method 410 may also include implanting a device through the second lumen and into the triangle of Koch region 420. The second lumen may direct the device from the implant location toward the LV apex, which may facilitate implanting the device for VfA cardiac therapy. Once in position, the device may be fixed at the implant location. The method 410 may include removing the delivery catheter 422. For example, the delivery catheter may be slit and retracted.

FIG. 9 is a flow diagram showing another example of a method 430 of using a therapy catheter (e.g., EP catheter) for the elongated element and an integrally formed delivery-catheter defining a first lumen and a second lumen. The method 430 may include advancing a therapy catheter into the CS 432. In particular, the therapy catheter may be inserted over a guidewire into the subclavian vein and traverse through the SVC to enter the RA and then used to cannulate the CS. The therapy catheter may be anchored in the CS. For example, the therapy catheter may be advanced more than a few centimeters into the CS and even into the great cardiac vein (GCV) to anchor the therapy catheter in the CS. A guidewire may also be advanced into the CS through the therapy catheter in a similar manner.

The method 430 may also include advancing the delivery catheter, or dual-lumen catheter, over the therapy catheter toward the CS using the first lumen of the delivery catheter 416. The delivery catheter may be tracked along the therapy catheter until the delivery catheter prevents further advancement. For example, a portion forming the second lumen may be impeded from further advancement by the CS ostium.

The method 430 may include orienting the second lumen of the delivery catheter toward the triangle of Koch region of the patient's heart 436. In some embodiments, the delivery catheter is torqued so that the second portion of the delivery catheter defining the second lumen, which may have a fixed or deflectable curve, comes into contact with the tissue in the target implant location in the triangle of Koch region.

The method 430 may also include implanting a device through the second lumen and into the triangle of Koch region 438. The second lumen may direct the device from the implant location toward the LV apex, which may facilitate implanting the device for VfA cardiac therapy. Once in position, the device may be fixed at the implant location. The method 430 may include removing the delivery catheter 440. For example, the delivery catheter may be slit and retracted. The therapy catheter may remain or be removed. The guidewire may also be removed, for example, when the delivery catheter is removed.

FIG. 10 is a flow diagram showing another example of a method 450 of using a guidewire for the elongated element and a separably formed delivery-catheter with translatable first and second portions. The method 450 may include advancing a first portion of the delivery catheter over a guidewire 452. In particular, the first portion defining the first lumen may be inserted over a guidewire into the subclavian vein and traverse through the SVC to enter the RA and then used to cannulate the CS. The guidewire may be advanced into the CS through the first lumen.

The method 450 may include translatably coupling the first and second portions using an interlocking assembly, such as a channel and complementary protrusion, 454. In particular, a protrusion of the second portion may be inserted into the channel of the first portion.

The method 450 may include advancing the second portion defining the second lumen over the first portion toward the CS 456. The protrusion of second portion may be tracked along the channel of the first portion until the second portion prevents further advancement. For example, the second portion forming the second lumen may be impeded from further advancement by the CS ostium.

The method 450 may include orienting the second lumen of the second portion toward the triangle of Koch region of the patient's heart 458. In some embodiments, the delivery catheter is torqued so that the second portion of the delivery catheter, which may have a fixed or deflectable curve, comes into contact with the tissue in the target implant location in the triangle of Koch region.

The method 450 may also include implanting a device through the second lumen and into the triangle of Koch region 460. The second lumen may direct the device from the implant location toward the LV apex, which may facilitate implanting the device for VfA cardiac therapy. Once in position, the device may be fixed at the implant location. The method 450 may include removing the delivery catheter 462. For example, the delivery catheter may be slit and retracted.

ILLUSTRATIVE EMBODIMENTS

While the present disclosure is not so limited, an appreciation of various aspects of the disclosure will be gained through a discussion of the specific illustrative embodiments provided below. Various modifications of the illustrative embodiments, as well as additional embodiments of the disclosure, will become apparent herein.

In illustrative embodiment A1, an implantable medical device delivery system includes an elongated element anchorable in the coronary sinus (CS) of a patient's heart. The system also includes a delivery catheter with an elongated body having a first portion defining a first lumen and a second portion defining a second lumen. The first lumen in a first distal end region of the first portion extends along a first axis and the second lumen in a second distal end region of the second portion extends along a second axis forming an angle with the first axis. The second axis points toward the left ventricular (LV) apex of the patient's heart when the anchorable elongated element is advanced through the first lumen into the CS.

In illustrative embodiment A2, the system of any A illustrative embodiment further includes the delivery catheter configured such that an implantable medical device advanced through the second lumen is directed to an implantation site in the triangle of Koch region of the patient's heart when the elongated element is advanced through the first lumen into the CS and the second axis points to the LV apex.

In illustrative embodiment A3, the system of illustrative embodiment A2 further includes the implantable medical device. The implantable medical device includes at least one electrode to provide cardiac therapy to or sense electrical activity of the right atrium (RA) or the LV of the patient's heart.

In illustrative embodiment A4, the system of any A illustrative embodiment further includes the implantable medical device being a leaded implantable medical device.

In illustrative embodiment A5, the system of any A illustrative embodiment further includes the angle being a fixed angle.

In illustrative embodiment A6, the system of any A illustrative embodiment further includes the elongated element being a guidewire or a catheter.

In illustrative embodiment A7, the system of any A illustrative embodiment further includes the elongated element having one or both of an anchorable balloon and an anchorable side helix.

In illustrative embodiment A8, the system of any A illustrative embodiment further includes the elongated element having one or more electrodes.

In illustrative embodiment A9, the system of any A illustrative embodiment further includes one or more electrodes coupled to the second distal end region of the second portion to map atrial activation

In illustrative embodiment A10, the system of any A illustrative embodiment further includes the second distal end region being more flexible than one or both of the proximal region of the elongated body and the elongated element.

In illustrative embodiment A11, the system of any A illustrative embodiment further includes the second distal end region being distal to the first distal end region relative to the first axis.

In illustrative embodiment A12, the system of any A illustrative embodiment further includes the angle being at most 90 degrees.

In illustrative embodiment B1, a delivery catheter includes a first portion advanceable into the coronary sinus (CS) of a patient's heart having an elongated body defining a first lumen and an exterior channel. When the first portion is advanced into the CS, a region of the first portion adjacent to the CS ostium of the patient's heart extends along a first axis. The device includes a second portion having an elongated body defining a second lumen and having a laterally-extending protrusion configured to be received into the exterior channel of the first portion to slidably guide the second portion along a length of the first portion. A distal end region of the second portion extends along a second axis when the protrusion is engaged in the channel forming a fixed angle with the first axis such that the second axis points toward the left ventricular (LV) apex of the patient's heart when the first portion is advanced into the CS.

In illustrative embodiment B2, the system of any B illustrative embodiment further includes an implantable medical device advanced through the second lumen being directed to an implantation site in the triangle of Koch region of the patient's heart when the first portion is advanced into the CS and the second axis points to the LV apex.

In illustrative embodiment B3, the system of illustrative embodiment B2 further includes the implantable medical device. The implantable medical device includes at least one electrode to provide cardiac therapy to or sense electrical activity of the right atrium (RA) or the LV of the patient's heart.

In illustrative embodiment B4, the system of any B illustrative embodiment further includes the protrusion being disposed at a discrete location on the elongated body of the second portion.

In illustrative embodiment B5, the system of any B illustrative embodiment further includes one or more electrodes being coupled to the distal end region of the second portion to map atrial activation.

In illustrative embodiment C1, a method of delivering an implantable medical device includes advancing a first distal end region of a first portion of a dual-lumen catheter toward the coronary sinus (CS) of a patient's heart. The first portion defines a first lumen and the first distal end region extends along a first axis. The method includes orienting a second distal end region of a second portion of the dual-lumen catheter toward the triangle of Koch region of the patient's heart. The second portion defines a second lumen and the second distal end region extends along a second axis forming an angle with the first axis such that the second axis points toward the left ventricular (LV) apex of the patient's heart when the first distal end region is fully advanced toward the CS.

In illustrative embodiment C2, the method of any C illustrative embodiment further includes rotating the dual-lumen catheter to point the second axis toward the LV apex, advancing an implantable medical device through the second lumen of the dual-lumen catheter, and fixing the implantable medical device to an implantation site in the triangle of Koch region of the patient's heart.

In illustrative embodiment C3, the method of any C illustrative embodiment further includes advancing an elongated element into the coronary sinus (CS) of the patient's heart. When the elongated element is advanced into the CS, a portion of the elongated element adjacent to the CS ostium extends along the first axis. The method includes advancing the dual-lumen catheter over the elongated element using the first lumen to guide the first distal end region toward the CS.

In illustrative embodiment C4, the method of illustrative embodiment C3 further includes the elongated element having a guidewire and the method further including advancing a cannulation catheter into the CS of the patient's heart, advancing the guidewire through the cannulation catheter into the CS, and removing the cannulation catheter.

In illustrative embodiment C5, the method of any C illustrative embodiment further includes the first portion defining an exterior channel and the second portion having a laterally-extending protrusion configured to be received into the exterior channel. The method includes advancing the second portion guided by first portion using the protrusion engaged with the exterior channel, orienting the second portion to point the second axis toward the LV apex, advancing an implantable medical device through the second lumen of the dual-lumen catheter, and fixing the implantable medical device to an implantation site in the triangle of Koch region of the patient's heart.

Thus, various embodiments of the DELIVERY SYSTEMS FOR VFA CARDIAC THERAPY are disclosed. The techniques of the present disclosure provide a delivery catheter that stabilizes an implantable medical device at an appropriate location and orientation for implantation at a target implant region, particularly in the triangle of Koch region to deliver pacing to the LV, using the CS as a physical reference.

It should be understood that various aspects disclosed herein may be combined in different combinations than the combinations specifically presented in the description and accompanying drawings. It should also be understood that, depending on the example, certain acts or events of any of the processes or methods described herein may be performed in a different sequence, may be added, merged, or left out altogether (e.g., all described acts or events may not be necessary to carry out the techniques). In addition, while certain aspects of this disclosure are described as being performed by a single module or unit for purposes of clarity, it should be understood that the techniques of this disclosure may be performed by a combination of units or modules associated with, for example, a medical device.

In one or more examples, the described techniques may be implemented in hardware, software, firmware, or any combination thereof. If implemented in software, the functions may be stored as one or more instructions or code on a computer-readable medium and executed by a hardware-based processing unit. Computer-readable media may include non-transitory computer-readable media, which corresponds to a tangible medium such as data storage media (e.g., RAM, ROM, EEPROM, flash memory, or any other medium that can be used to store desired program code in the form of instructions or data structures and that can be accessed by a computer).

Instructions may be executed by one or more processors, such as one or more digital signal processors (DSPs), general purpose microprocessors, application specific integrated circuits (ASICs), field programmable logic arrays (FPGAs), or other equivalent integrated or discrete logic circuitry. Accordingly, the term “processor” as used herein may refer to any of the foregoing structure or any other physical structure suitable for implementation of the described techniques. Also, the techniques could be fully implemented in one or more circuits or logic elements.

All references and publications cited herein are expressly incorporated herein by reference in their entirety for all purposes, except to the extent any aspect directly contradicts this disclosure.

All scientific and technical terms used herein have meanings commonly used in the art unless otherwise specified. The definitions provided herein are to facilitate understanding of certain terms used frequently herein and are not meant to limit the scope of the present disclosure.

Unless otherwise indicated, all numbers expressing feature sizes, amounts, and physical properties used in the specification and claims may be understood as being modified either by the term “exactly” or “about.” Accordingly, unless indicated to the contrary, the numerical parameters set forth in the foregoing specification and attached claims are approximations that can vary depending upon the desired properties sought to be obtained by those skilled in the art utilizing the teachings disclosed herein or, for example, within typical ranges of experimental error.

The recitation of numerical ranges by endpoints includes all numbers subsumed within that range (e.g. 1 to 5 includes 1, 1.5, 2, 2.75, 3, 3.80, 4, and 5) and any range within that range. Herein, the terms “at most” or “no greater than” a number (e.g., up to 50) includes the number (e.g., 50), and the term “at least” or “no less than” a number (e.g., no less than 5) includes the number (e.g., 5).

Terms related to orientation, such as “proximal,” “distal,” “side,” and “end,” are used to describe relative positions of components and are not meant to limit the orientation of the embodiments contemplated.

The terms “coupled” or “connected” refer to elements being attached to each other either directly (in direct contact with each other) or indirectly (having one or more elements between and attaching the two elements). Either term may be modified by “operatively” and “operably,” which may be used interchangeably, to describe that the coupling or connection is configured to allow the components to interact to carry out functionality.

As used herein, the term “configured to” may be used interchangeably with the terms “adapted to” or “structured to” unless the content of this disclosure clearly dictates otherwise.

Th singular forms “a,” “an,” and “the” encompass embodiments having plural referents unless its context clearly dictates otherwise.

The term “or” is generally employed in its inclusive sense, for example, to mean “and/or” unless the context clearly dictates otherwise.

The term “and/or” means one or all of the listed elements or a combination of at least two of the listed elements.

The phrases “at least one of,” “comprises at least one of,” and “one or more of” followed by a list refers to any one of the items in the list and any combination of two or more items in the list.

As used herein, “have,” “having,” “include,” “including,” “comprise,” “comprising” or the like are used in their open-ended sense, and generally mean “including, but not limited to.” It will be understood that “consisting essentially of,” “consisting of,” and the like are subsumed in “comprising,” and the like.

Reference to “one embodiment,” “an embodiment,” “certain embodiments,” or “some embodiments,” etc., means that a particular feature, configuration, composition, or characteristic described in connection with the embodiment is included in at least one embodiment of the disclosure. Thus, the appearances of such phrases in various places throughout are not necessarily referring to the same embodiment of the disclosure. Furthermore, the particular features, configurations, compositions, or characteristics may be combined in any suitable manner in one or more embodiments.

Claims

1. A method of delivering an implantable medical device comprising: advancing a first distal end region of a first portion of a dual-lumen catheter toward the coronary sinus (CS) of a patient's heart, wherein the first portion defines a first lumen and the first distal end region extends along a first axis; andorienting a second distal end region of a second portion of the dual-lumen catheter toward the triangle of Koch region of the patient's heart, wherein the second portion defines a second lumen and the second distal end region extends along a second axis forming an angle with the first axis such that the second axis points toward the left ventricular (LV) apex of the patient's heart when the second portion is located in the right atrium (RA) and the first distal end region is fully advanced toward the CS wherein, the angle is between 30 degree to 110 degree.

2. The method according to claim 1, further comprising: rotating the dual-lumen catheter to point the second axis toward the LV apex;advancing an implantable medical device through the second lumen of the dual-lumen catheter; andfixing the implantable medical device to an implantation site in the triangle of Koch region of the patient's heart.

3. The method according to claim 1, further comprising: advancing an elongated element into the coronary sinus (CS) of the patient's heart, wherein when the elongated element is advanced into the CS, a portion of the elongated element adjacent to the CS ostium extends along the first axis; andadvancing the dual-lumen catheter over the elongated element using the first lumen to guide the first distal end region toward the CS.

4. The method according to claim 3, wherein the elongated element comprises a guidewire, and the method further comprises: advancing a cannulation catheter into the CS of the patient's heart;advancing the guidewire through the cannulation catheter into the CS; andremoving the cannulation catheter.

5. The method according to claim 1, wherein the first portion defines an exterior channel and the second portion comprises a laterally-extending protrusion configured to be received into the exterior channel, further comprising: advancing the second portion guided by first portion using the protrusion engaged with the exterior channel;orienting the second portion to point the second axis toward the LV apex;advancing an implantable medical device through the second lumen of the dual-lumen catheter; and