Transvenous intracardiac pacing catheter

Abstract

The embodiments described herein relate to a self-positioning, quick-deployment low profile transvenous electrode system for sequentially pacing both the atrium and ventricle of the heart in the “dual chamber” mode, and methods for deploying the same.

Description

BACKGROUND

The embodiments described herein relate generally to medical devices that provide heart pacemaking function, and more particularly to a temporary easily insertable transvenous dual-chamber sequential pacing catheter, and systems and methods for atrio-ventricular pacing to achieve AV synchrony.

The heart requires to be paced temporarily during or after certain medical procedures or conditions like open heart surgery, heart attack, some infections, electrolyte disturbances, cardiac trauma or other issues. The only available temporary pacing catheters will not pace the heart in atrio-ventricular (AV) synchrony (only the right ventricle is paced).

Establishing and maintaining atrio-ventricular (AV) synchrony in a patient is important for achieving optimal cardiovascular hemodynamics. AV synchrony is estimated to increase stroke volume by as much as 50% in a normal heart and increase cardiac index by as much as 25% to 30%.

After open heart surgery, pacing is performed using epicardial wires that are lightly sutured to the epicardium before the thorax is closed. Once these epicardial wires are no longer needed, these pacing wires are pulled through the skin. Pulling the pacing wires represents a risk of a cardiac tamponade that can lead to death, and can also pose a risk of infection, myocardial damage, ventricular arrhythmias and perforation.

Existing temporary pacing catheters are also difficult to position correctly and often add complications including, in the case of balloon positioning, having the catheter move to and block the right ventricle outflow tract and the pulmonary artery.

Existing pacing catheter leads can also move (dislodge) either while pacing or at a critical point during a specific procedure like rapid pacing. For this reason, the mobility of the patient (ambulation) is limited when being temporary paced. Limited ambulation is known to increase the length of stay in certain scenarios and lead to higher healthcare costs.

Accordingly, there is a need for an AV sequential pacing catheter that is easy to insert and position on the right chambers of the heart to replace the current available temporary catheters/leads.

SUMMARY

The embodiments described herein are directed to an insertable atrio-ventricular sequential pacing catheter that is easy to insert and position on the right chambers of the heart.

The present disclosure relates to an improved transvenous intracardiac pacing catheter, and particularly to devices, methods, and systems for establishing and maintaining atrio-ventricular (AV) synchrony in a patient by providing an insertable atrio-ventricular sequential pacing catheter system having an inner catheter, outer catheter and connector assembly. In a preferred embodiment, the inner catheter incorporates seven nitinol PTFE heat shrink set of wires with radiopaque tips. Four of the wires are leads for the atrium, two are for the ventricle and one forms the distal tip with cap. The wires are incorporated into a seven lumen extrusion and fitted into correct position using fixtures. In a preferred embodiment, the outer catheter is a multi-durometer, coil reinforced catheter with luer hub and radiopaque tip. In a preferred embodiment, the connector assembly attached the wires to plugs for connection to the pulse transmission unit.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a schematic view of one embodiment of the device, illustrating the atrial leads, the ventricular leads, the retractable sheath, the combined hub and terminal connection, and steerable deployment mechanism, and the external lead terminals, according to the invention.

FIG. 2 is a schematic view another embodiment of the device, illustrating the atrial leads, the ventricular leads, the retractable sheath, the hub, the independent terminal connection, and steerable deployment mechanism, and the external lead terminals, according to the invention.

FIG. 3 is a schematic of the two-inner sheath (dual lumen) embodiment illustrating the outer steerable catheter sheath housing the two inner sheaths, with one inner sheath having the ventricle leads and the other inner sheath having the atrium leads, according to the invention.

FIG. 4 is a schematic of the seven-inner sheath (multi-lumen) embodiment illustrating the outer steerable catheter sheath housing the seven inner sheaths, with each inner sheath its own lead, and providing three (3) ventricle leads and four (4) atrium leads, according to the invention.

FIG. 5 is a schematic of a cross-section of the seven-inner sheath (multi-lumen) embodiment illustrating the outer steerable catheter sheath housing the seven inner sheaths, with each inner sheath its own lead, and providing three (3) ventricle leads and four (4) atrium leads, according to the invention.

FIG. 6 is a schematic view of a cross-section of a human heart, a plurality of electrodes inserted in the ventricle and atrium contacting the walls of the heart chambers and a pacer, according to the invention.

FIG. 7 is a chart of an acute first in human study and is useful to support an embodiment of the present invention. FIG. 5 shows an example study of a sample of 10 patients, although not necessarily for any specific indication. FIG. 5 shows that procedure time can average 24 minutes to position and deploy the device, pace the RV, pace the A synchronize AV pacing, perform a left side diagnostic, and the pace the RV, pace the A, synchronize the AV pacing, and remove the device, according to the invention.

FIG. 8 is an example of a chart of data in an embodiment of the invention from a procedure recording a non-limiting preferred embodiment. FIG. 8 shows by subject and lead, the impedance, the threshold, and the current, recorded. This shows safe delivery with and without fluoroscopic guidance, successful pacing, excellent contact and hold of the leads against the cardiac tissue, with no adverse events or significant adverse events at discharge, according to the invention.

FIGS. 9A, 9B, 9C are illustrations of one embodiment of a device being introduced into the jugular vein of a patient, with removal of the guidewire, and introduction of the transvenous dual-chamber sequential pacing device into the steerable catheter sheath, according to the invention.

FIG. 10 is an illustration of one embodiment of the transvenous dual-chamber sequential pacing device deployed into a heart, as shown on fluoroscopic imaging, according to the invention.

FIG. 11 is an illustration of one embodiment of the transvenous dual-chamber sequential pacing device deployed into a heart, as shown on fluoroscopic imaging, according to the invention.

FIG. 12 is an illustration of one embodiment of the transvenous dual-chamber sequential pacing device deployed into a heart, as shown in a cut-away view into the heart, according to the invention.

FIG. 13 is an illustration of one embodiment of the transvenous dual-chamber sequential pacing device deployed into a heart, with ventricle leads deployed from a movable inner sheath into the ventricle, according to the invention.

FIG. 14 is an illustration of one embodiment of the transvenous dual-chamber sequential pacing device deployed into a heart, with atrium leads being deployed from a movable inner sheath into the atrium, while ventricle leads have already been deployed into the ventricle, according to the invention.

FIG. 15 is an illustration showing how the device can sense abnormal heart rhythm using the transvenous dual-chamber sequential pacing device deployed into a heart, according to the invention.

FIG. 16 is an illustration showing how the device can provide electrical stimulation to the atrium using the transvenous dual-chamber sequential pacing device deployed into a heart, according to the invention.

FIG. 17 is an illustration showing how the device can provide electrical stimulation to the ventricle using the transvenous dual-chamber sequential pacing device deployed into a heart, according to the invention.

FIG. 18 is an illustration showing how the device can sense the corrected normal heart rhythm using the transvenous dual-chamber sequential pacing device deployed into a heart, according to the invention.

FIG. 19 is an illustration showing how the device is removed after being deployed into a heart, according to the invention.

FIG. 20 is an illustration of a ventricle only embodiment of the invention.

DETAILED DESCRIPTION

Disclosed embodiments are directed to a self-positioning, quick-deployment low profile transvenous electrode system for sequentially pacing both the atrium and ventricle of the heart in the “dual chamber” mode, comprising a plurality of insulated electrical wires bundled together to form at least two in-line sets of leads is disclosed. The invention provides an emergency pacemaker that will pace and sense both atrial and ventricular chambers and provide “dual chamber” control of the heart using a lead that can be safely and easily inserted into the heart in an emergency situation. “Dual chamber” pacing refers to continuous monitoring of the spontaneous activity of the heart both in the atria and in the ventricles, interpreting the detected events according certain accepted algorithms and providing stimuli to the chambers as needed to maintain a physiologically appropriate rhythm. Importantly, the device can be deployed with and without fluoroscopic guidance. In one embodiment, a self-positioning feature allows the device to be used without the extensive training and specialist experience that has been historically required for pacing devices.

In some embodiments of the invention, the device comprises three (3) ventricular leads and four (4) atrial leads, made from shape memory material. Two of the three ventricular leads are bent at 90 degrees from the central axial lead and are 180 degrees from each other. The four atrial leads are bent at 90 degrees from the central axis (x-axis), and are each separated 90 degrees from the adjacent leads, in the y-axis plane.

In some embodiments of the invention, both sets of leads are mounted and contained inside a slender e.g. 8Fr (1 mm), tubular, flexible elongated e.g. 35 cm retaining sheath that serves as a guide and delivery system during insertion and removal of the electrode system. Each of the wires is surrounded individually by electrical insulation.

In some embodiments of the invention, the bundle of insulated wires can be arranged in either a parallel or helical configuration. In order to conform to heart chambers of different sizes, the leads will be produced in different lengths and appropriate distances between the electrodes.

In some embodiments of the invention, the electrode system is constructed by assembling a plurality of insulated superelastic electrically conductive wires. The insulation material separates each of the wires from each other, but the wires are mounted in a bundle as a single cable-like structure. At the proximal end, the electrodes are connected to an external pacemaker. At the distal end, the individual wires once inserted into the heart will make contact with either atrial or ventricular tissue. The distal ends of the individual wires may include spherical electrode contacts that will make contact with atrial tissue or ventricular tissue.

In some embodiments of the invention, each of the wires has memory and is pre-formed in a specific curvature but also is resilient enough to be contained in the sheath prior to being positioned within the heart chambers. Since both sets of leads for the ventricle and the atrium are contained inside a single slender flexible retaining sheath that is the guide and delivery system during insertion and removal of the electrode system, the ventricular electrode or electrodes which can be pacemaker sensors or stimulators are released first after the retaining sheath has been successfully inserted into the right ventricle. At this point, the sheath is retracted allowing the ventricle wire leads to escape from the sheath and because of each wire's pre-formed shape which has memory, spread out to individually contact the endocardial surfaces. The leads expand outwardly, engaging the tissue and chamber wall of the ventricle. If a mechanical parallel wire configuration is chosen in the sheath, the wires can be released and make contact in the same plane. Otherwise, the wires can be staggered within the ventricular chamber. If a helical configuration of the wires is chosen in the sheath, the wires are staggered upon release to cover different points of a chamber wall. Ideal wires for this configuration are disclosed in U.S. Pat. Nos. 6,137,060 and 3,699,886.

Continued retraction of the sheath will then allow the escape of the atrial wires and electrodes which also have memory and which, upon escape from the sheath, will proceed outwardly towards the atrial tissue for engagement.

As discussed above, in some embodiments of the invention, the distal ends of the individual wires may have spherical conductive ball tips to provide high current density and sensitivity. For the physician to effectively introduce the device transvenously, the sheath will have to be extended all the way forward initially such that it covers all the wires with the possible exception of the distal electrodes, which may protrude beyond the sheath during the introduction of the sheath with the conducting leads into the heart. The path of the sheath with the leads during insertion is into the subclavian or jugular vein past the atrium and into the ventricle. Once the electrode system reaches the apex of the right ventricle, the operator begins to pull back slowly on the sheath, thus releasing each wire individually until all necessary contact points are made.

In some embodiments of the invention, each wire is made of a superelastic or memory shape retention material such as Nitinol™, as the sheath is slowly pulled back the wires are released. Each wire will be pre-shaped with the proper orientation so that as the medical personnel, e.g. cardiac interventionalists, emergency medical technicians, surgical staff, outpatient staff, etc., pulls the sheath back, the wire fans outwardly until the wire tips rest against the interior wall of each chamber, thus making electrical contact. The memory in the wire will hold it in place within the chamber. The ball tip ending of each wire as well as the highly flexible chosen material will minimize trauma to the endocardium while allowing a sufficiently large surface area for electrical conduction.

Polymers

Any of the devices and/or components thereof may be fabricated from any suitable biocompatible material or combination of materials. For example, an outer chassis, and/or components thereof may be fabricated from biocompatible materials, metals, metal alloys, polymer coated metals, and/or the like. Suitable biocompatible materials, metals and/or metal alloys can include polymers, co-polymers, ceramics, glasses, aluminum, aluminum alloys, stainless steel (e.g., 316 L stainless steel), cobalt chromium (Co—Cr) alloys, nickel-titanium alloys (e.g., Nitinol®), and/or the like. Moreover, any of the chassis or components may be covered with a suitable polymer coating, and can include natural or synthetic rubber, polyethylene vinyl acetate (PEVA), poly-butyl methacrylate (PBMA), translute Styrene Isoprene Butadiene (SIBS) copolymer, polylactic acid, polyester, polylactide, D-lactic polylactic acid (DLPLA), polylactic-co-glycolic acid (PLGA), and/or the like.

In order for the electrode system within the sheath to freely navigate through the blood vessels, it must have a very smooth surface. Adequate flexibility must be achieved with materials that do not fracture or fail prematurely. The insulation material used to insulate each individual wire will be of the type used in the production of existing pacing leads. Furthermore, the sheath material used will be a thermoplastic elastomer similar to those used in the manufacture of catheters and for added strength it can be braided.

In one non-limiting embodiment, the electrode system in accordance with this invention may be designed primarily for emergency temporary use such that the leads described have passive fixation. However, in another non-limiting example, it is possible that the present invention can be utilized as part of a permanently implanted pacemaker system such that the electrode would become embedded in the heart tissue or actively attached to the endocardium by one of many means available for active fixation.

Some biocompatible synthetic material(s) can include, for example, polyesters, polyurethanes, polytetrafluoroethylene (PTFE) (e.g., Teflon), and/or the like. Where a thin, durable synthetic material is contemplated (e.g., for a covering), synthetic polymer materials such expanded PTFE or polyester may optionally be used. Other suitable materials may optionally include elastomers, thermoplastics, polyurethanes, thermoplastic polycarbonate urethane, polyether urethane, segmented polyether urethane, silicone polyether urethane, polyetheretherketone (PEEK), silicone-polycarbonate urethane, polypropylene, polyethylene, low-density polyethylene (LDPE), high-density polyethylene (HDPE), ultra-high density polyethylene (UHDPE), polyolefins, polyethylene-glycols, polyethersulphones, polysulphones, polyvinylpyrrolidones, polyvinylchlorides, other fluoropolymers, polyesters, polyethylene-terephthalate (PET) (e.g., Dacron), Poly-L-lactic acids (PLLA), polyglycolic acid (PGA), poly(D, L-lactide/glycolide) copolymer (PDLA), silicone polyesters, polyamides (Nylon), PT1-B, elongated PTFE, expanded PTFE, siloxane polymers and/or oligomers, and/or polylactones, and block co-polymers using the same.

Radiopaque Materials

Barium Sulfate. Barium sulfate (BaSO4) is a radiopaque material widely compounded in medical formulations and a common filler used with medical-grade polymers. It is an inexpensive material, costing approximately $2/lb; and its white color can be changed with the addition of colorants.

With a specific gravity of 4.5, barium sulfate is generally used at loadings of 20 to 40% by weight. While a 20% barium sulfate compound is typical for general-purpose medical device applications, some practitioners prefer a higher degree of radiopacity than can be provided by that loading. With striped tubing, for example, a 40% compound is standard.

A loading of 20% barium sulfate by weight is equivalent to about 5.8% by volume; 40% by weight equals 14% by volume. As the barium content moves beyond about 20% by volume, compounds begin to show losses of the base polymer's tensile strength and other mechanical properties. It is therefore best to formulate radiopacifiers at the minimum level for each application; excessive use of these fillers is not recommended.

Bismuth. Considerably more expensive than barium at $20 to $30/lb (depending on the chemical salt selected), bismuth compounds are also twice as dense. Bismuth trioxide (Bi2O3), which is yellow in color, has a specific gravity of 8.9; bismuth subcarbonate (Bi2O2CO3) has a specific gravity of 8.0; and bismuth oxychloride (BiOCl) has a specific gravity of 7.7. Because of the density, a 40% bismuth compound contains only about half the volume ratio as a 40% barium sulfate compound. Since bismuth produces a brighter, sharper, higher-contrast image on an x-ray film or fluoroscope than does barium, it is commonly used whenever a high level of radiopacity is required.

Compared with barium, higher loadings are also possible: even a 60% bismuth compound can maintain the same base polymer mechanical properties as a 40% barium sulfate compound. A 20% bismuth loading by weight equals 3% by volume; a 40% loading by weight equals 7.6% by volume. Bismuth is sensitive to compounding and must be treated gently, with low-shear mixing recommended for optimum results. Bismuth provides high levels of radiopacity.

Tungsten. A fine metal powder with a specific gravity of 19.35, tungsten (W) is more than twice as dense as bismuth and can provide a high attenuation coefficient at a cost of approximately $20/lb. A loading of 60% tungsten has approximately the same volume ratio as a 40% bismuth compound. Devices can be made highly radiopaque with relatively low loadings of tungsten, enabling good mechanical properties to be maintained. Because of its density, tungsten is typically selected as a filler for very-thin-walled devices.

A 50% tungsten loading by weight equals only 5.4% by volume; an 80% loading by weight represents 18.5% by volume. Tungsten is black in color, which cannot be changed with colorants. It is abrasive and can cause accelerated wear in extruders and other processing equipment. Devices filled with high loadings of tungsten will exhibit surface roughness. Because the material invites oxidation in the presence of oxygen and heat and is highly flammable, care should be taken while drying it. With elastomers, barium sulfate mixes better than do tungsten or bismuth compounds.

Compounding Considerations

Newer x-ray machines generally operate at higher energy levels than older ones—typically at 80 to 125 kVp as compared with 60 to 80 kVp for older machines. Higher energy radiation increases the transmission of photons and can require higher levels of radiopacity to provide the desired attenuation. Therefore, devices produced with barium sulfate compounds might not appear as bright on newer machines, for which bismuth compounds would be a better choice of radiopaque filler. Blending these materials, however, can often be the best solution, especially for multipurpose formulations used over a broad range of energy levels. A blend of barium, easily attenuated at low energy levels, and bismuth, attenuated at higher levels, often works well.

Compounding radiopaque materials includes factoring in the degree of attenuation of the device, the tensile strength, elongation, and other mechanical properties of the polymers. Fillers, antioxidants, stabilizers, and colorants may also be included with metallic fillers.

The present invention can be used in emergency rooms, after open heart surgery, during or after minimally invasive heart surgery or implant procedures such as valve repair or replacement, in intensive care units, at the bedsides, cardiac catheterization labs, ambulances, battle fields and other emergency settings where patients with heart block or other life threatening arrhythmias may be found.

Independent Claims

In a preferred embodiment, the invention provides a self-positioning, quick-deployment low profile transvenous electrode system for pacing of a heart, comprising:

• • a pacemaker including a pulse generator that can provide sensing and stimuli for a ventricle or an atrium;
  • a plurality of insulated electrical wires bundled together to form a distal set of three (3) ventricle leads disposed within a first inner sheath, and a proximal set of four (4) atrium leads disposed within a second inner sheath, the first inner sheath and the second inner sheath disposed within an outer steerable catheter sheath,
  • said outer steerable catheter sheath being movable from said first inner sheath and said second inner sheath once inserted into the heart for deploying the first inner sheath to the ventricle and the second inner sheath to the atrium, said outer steerable catheter sheath being entirely removed from the atrium and ventricle when the transvenous electrode system is engaged,
  • said first inner sheath being movable to expose the distal set of three (3) ventricle leads to the ventricle, and said second inner sheath being movable to expose the four (4) atrium leads to the atrium,
  • the first inner sheath and the second inner sheath each made from a polymer, wherein the polymer is doped with a radiopaque material to form a radiopaque polymer sheath or is labelled with at least one radiopaque marker element,
  • each of the ventricular and atrial leads have a proximal body portion, a distal end portion, and a tip portion,
  • the proximal body portion made from a radiopaque polymer-covered copper wire,
  • the distal end portion made from shape memory material, the shape memory material selected from stainless steel, spring steel, cobalt-chromium alloy, nickel-titanium alloy, and mixtures thereof,
  • the tip portion made from shape memory material and a radiopaque material, the radiopaque material selected from a barium-containing compound, a bismuth-containing compound, a steel compound, a tungsten-containing compound, and mixtures thereof,
  • two of the three ventricle leads are shape-set at a 90 degree angle in an expanded configuration, and the two ventricle leads are offset 180 degrees from each other, one of the three ventricle leads is a central axial lead,
  • each of the four atrium leads are shape-set at a 90 degree angle in an expanded configuration, and each of the four atrium leads are separated 90 degrees from each other,
  • the steerable catheter sheath is comprised of a distal portion and a proximal portion, and has a distance marker every 10 cm along its entire length,
  • the distal portion of the steerable catheter sheath is 5 cm in length and has a 0.010″ pitch coil and a biocompatible polymer cover,
  • the proximal portion of the steerable catheter sheath is 30 cm in length, has a 0.020″ pitch coil, a biocompatible polymer cover, at a proximal end of the proximal portion has a hub element, a Touhy-Borst access connector with a side port, an actuator dial that allows the steerable catheter sheath to be shaped and controlled, a deployment stop, and a cable junction housing,
  • atrium lead terminals and ventricle lead terminals extend from the cable junction housing to the pacemaker, wherein the pacemaker comprises computer program instructions readable by a processor to provides functions selected from the group consisting of: a diagnostic function, a sensor operation, a stimulation signal, a program for an individual lead for sensing, a program to reduce over-sensing of the ventricular leads by T-waves or other noise or attenuating or interfering signals, a program to reduce over-sensing of the atrium leads by the R-wave, a program to minimize cross-talk, and a program to adjust sensing and stimulation on a lead-by-lead basis;
  • the atrium leads shape-set to sense and stimulate an SA node area and an AV node area of the heart, the ventricle leads shape set to sense and stimulate a Bundle of His area, an Apex-Purkinje fiber area, and a Free-wall Purkinje area,
  • each of said ventricular leads connected to a ventricular sensor or stimulator in said pacemaker and each of said atrium leads connected to an atrium sensor or stimulator in said pacemaker.

Ventricle Only

In another preferred embodiment, the invention may provide a self-positioning, quick-deployment low profile transvenous electrode system for pacing of a heart, comprising:

• • a pacemaker including a pulse generator that can provide sensing and stimuli for a ventricle;
  • a pair of insulated electrical wires to form a first ventricle lead and a second ventricle lead, the first and the second ventricle leads disposed within an outer steerable catheter sheath,
  • said outer steerable catheter sheath being movable from said first and said second ventricle leads once inserted into the heart for deploying the first ventricle lead and the second ventricle lead to the ventricle, said outer steerable catheter sheath being entirely removed from the ventricle when the transvenous electrode system is engaged,
  • each of the first and the second ventricle leads have a proximal body portion, a distal end portion, and a tip portion,
  • the proximal body portion made from a radiopaque polymer-covered copper wire,
  • the distal end portion made from shape memory material, the shape memory material selected from stainless steel, spring steel, cobalt-chromium alloy, nickel-titanium alloy, and mixtures thereof,
  • the tip portion made from shape memory material and a radiopaque material, the radiopaque material selected from a barium-containing compound, a bismuth-containing compound, a steel compound, a tungsten-containing compound, and mixtures thereof,
  • the two ventricle leads are offset 180 degrees from each other,
  • the steerable catheter sheath is about 1.3 mm diameter or 4 French and is comprised of a distal portion and a proximal portion, and has a distance marker every 10 cm along its entire length,
  • the distal portion of the steerable catheter sheath is 5 cm in length and has a 0.010″ pitch coil and a biocompatible polymer cover,
  • the proximal portion of the steerable catheter sheath is 30 cm in length, has a 0.020″ pitch coil, a biocompatible polymer cover, at a proximal end of the proximal portion has a hub element, a Touhy-Borst access connector with a side port, an actuator dial that allows the steerable catheter sheath to be shaped and controlled, a deployment stop, and a cable junction housing,
  • atrium lead terminals and ventricle lead terminals extend from the cable junction housing to the pacemaker, wherein the pacemaker comprises computer program instructions readable by a processor to provides functions selected from the group consisting of: a diagnostic function, a sensor operation, a stimulation signal, a program for an individual lead for sensing, a program to reduce over-sensing of the ventricular leads by T-waves or other noise or attenuating or interfering signals, a program to minimize cross-talk, and a program to adjust sensing and stimulation on a lead-by-lead basis;
  • the ventricle leads shape set to sense and stimulate a Bundle of His area and a Free-wall Purkinje area,
  • each of said ventricular leads connected to a ventricular sensor or stimulator in said pacemaker.

Independent Sheathing

Any of the embodiments herein, including the ventricle embodiment, may include wherein the (first) ventricle lead is disposed within a (first) movable inner sheath, and the (second) ventricle lead is disposed within a (second) movable inner sheath, the inner sheath each made from a polymer, wherein the polymer is doped with a radiopaque material to form a radiopaque polymer sheath or is labelled with at least one radiopaque marker element.

Bundle Sheathing

Any of the embodiments herein may include wherein said first inner sheath is a set of three independently movable inner sheaths, each of the three (3) ventricle leads having its own movable sheath, and wherein said second inner sheath is a set of four (4) independently movable inner sheaths, each of the four (4) atrium leads having its own movable sheath.

Variations

Any of the dual chamber embodiments herein may include wherein the pacemaker includes two sequential pulse generators that can provide sensing and stimuli for a ventricle and an atrium for sequentially pacing both the atrium and ventricle of a heart in the “dual chamber” mode.

Any of the embodiments of the present invention may include 4 atrial, and 3 ventricular wires in a configuration where the atrial are 90 degrees from each about a Y-axis, and where the ventricular are in a planar configuration that is perpendicular to the central X-axis.

Any of the embodiments of the present invention may include wherein the atrial leads and ventricle leads have uninsulated wire in certain locations.

Any of the embodiments of the present invention may include wherein the copper body portion is braided or bonded to the distal end portion, where the distal end portion is steel or NiTi alloy.

Any of the embodiments of the present invention may include wherein the shape-setting of the eyelet is performed at the same time as the shape-setting of the played portion of the leads.

Any of the embodiments of the present invention may include wherein the shape-setting is performed faster by changing the wire cross section.

Any of the embodiments of the present invention may include wherein the tip of electrode is an eyelet not ball, and wherein the tip portion is a composite of a shape memory material and a radiopaque material.

Any of the embodiments of the present invention may include wherein the radiopaque materials are Tungsten, Barium, and/or Bismuth compounds. In particular, Bismuth provides a brighter luminescence under Xray. Bismuth compounds include Bi2O3, Bi2O2CO3, and BiOCl. Barium sulfate provides excellent compounding with polymer coatings, such as polyimides. Barium radiopaque polymers may be used for the catheter sheath/jacket, eyelet, as an RO band, and on other electrode portions, and sheath portions.

Any of the embodiments of the present invention may include wherein the polymer is polyimide, or where the polymer is silicone plus a lubricity agent, is made from PebaSlix 35D, is made from Pebax 72D, and the like.

Any of the embodiments of the present invention may include wherein the sheath is configured to provide a 90 degree curve over a 2.5″ diameter bend, and is also configured to provide a hockey-stick bend at a 45 degree angle+/−5 degrees.

Computer Programs

In another preferred embodiment, the invention provides wherein the invention includes computer program instructions executable on a processor for performing one or more functions selected from: decreasing sensitivity of certain leads and increasing sensitivity of other leads during a depolarization cycle (PQRST) allows the invention to increase SNR in the sensing function, decreasing or increasing stimulatory signals to one or more leads allows the invention to more accurately provide stimulation to the AV node, the SA node, the ventricular apex, or other cardiac tissue to provide a level of granularity to the stimulation function, programming leads so that sensing leads are not required to share the function of a shocking/stimulation leads, and bypassing damaged or degraded leads to allow continued functioning without requiring the entire device to be removed from a patient, this increasing the longevity of implanted devices using the inventive technology.

Methods

In another preferred embodiment, the invention provides a computer-implemented method for quickly deploying a cardiac pacing device to a heart in a patient, comprising:

• • (i) Providing the transvenous, dual-chamber dual-lumen system claimed and described herein;
  • (ii) Accessing a jugular vein in the patient and advancing the catheter sheath under ultrasound or other non-fluoroscopic imaging modality to a right ventricle of the heart of the patient;
  • (iii) Withdrawing the outer steerable catheter sheath to a first position to expose the first inner sheath and the second inner sheath;
  • (iv) Withdrawing the first inner sheath to a second position to expose and actuate the ventricle leads to connect with the ventricle tissue;
  • (iv) Withdrawing the second inner sheath to a third position to expose and actuate the atrium leads to connect with atrium tissue;
  • (v) Using computer program instructions executable on a processor, Performing a diagnostic test to identify the patient cardiac patterns and to validate the operation of the system;
  • (vi) Using computer program instructions executable on a processor, Performing a cardiac pacing routine appropriate as a treatment for the patent cardiac pattern;
  • (vii) Removing the catheter sheath and allowing the system to remain within the patient;
  • wherein performing steps (i)-(vii) are performed in a time period no longer than 60 minutes.

In another preferred embodiment, the invention provides, wherein performing steps (i)-(vii) are performed in a time period no longer than 30 minutes.

In another preferred embodiment, the invention provides a transvenous electrode system for heart block use in an emergency situation that is low cost, safe and reliable for pacing both the atrium and ventricle chambers of the heart of a patient with a heart block.

In another preferred embodiment, the invention provides an emergency heart pacemaker that requires only a small incision to insert the lead that will provide dual chamber (sequential) pacing and sensing for the atrial and ventricles of the heart.

In another preferred embodiment, the invention provides emergency pacemaker that will avoid problems of single chamber ventricular pacing so that the present invention provides for atrial-ventricular synchrony.

Definitions

The terminology used herein is for the purpose of describing particular embodiments only and is not intended to limit the full scope of the claims. Unless defined otherwise, all technical and scientific terms used herein have the same meanings as commonly understood by one of ordinary skill in the art. Nothing in this disclosure is to be construed as an admission that the embodiments described in this disclosure are not entitled to antedate such disclosure by virtue of prior invention.

As used herein, the singular forms “a”, “an” and “the” are intended to include the plural forms as well, unless the context clearly indicates otherwise. With respect to the use of substantially any plural and/or singular terms herein, those having skill in the art can translate from the plural to the singular and/or from the singular to the plural as is appropriate to the context and/or application. The various singular/plural permutations may be expressly set forth herein for sake of clarity.

In general, terms used herein, and especially in the appended claims (e.g., bodies of the appended claims) are generally intended as “open” terms (e.g., the term “including” should be interpreted as “including but not limited to,” the term “having” should be interpreted as “having at least,” etc.). Similarly, the terms “comprises” and/or “comprising,” when used in this specification, specify the presence of stated features, integers (or fractions thereof), steps, operations, elements, and/or components, but do not preclude the presence or addition of one or more other features, integers (or fractions thereof), steps, operations, elements, components, and/or groups thereof. As used in this document, the term “comprising” means “including, but not limited to.”

As used herein the term “and/or” includes any and all combinations of one or more of the associated listed items. It should be understood that virtually any disjunctive word and/or phrase presenting two or more alternative terms, whether in the description, claims, or drawings, should be understood to contemplate the possibilities of including one of the terms, either of the terms, or both terms. For example, the phrase “A or B” will be understood to include the possibilities of “A” or “B” or “A and B.”

All ranges disclosed herein also encompass any and all possible subranges and combinations of subranges thereof unless expressly stated otherwise. Any listed range should be recognized as sufficiently describing and enabling the same range being broken down into at least equal subparts unless expressly stated otherwise. As will be understood by one skilled in the art, a range includes each individual member.

The embodiments herein, and/or the various features or advantageous details thereof, are explained more fully with reference to the non-limiting embodiments that are illustrated in the accompanying drawings and detailed in the following description. Descriptions of well-known components and processing techniques are omitted so as to not unnecessarily obscure the embodiments herein. Like numbers refer to like elements throughout.

The examples and/or embodiments described herein are intended merely to facilitate an understanding of structures, functions, and/or aspects of the embodiments, ways in which the embodiments may be practiced, and/or to further enable those skilled in the art to practice the embodiments herein. Similarly, methods and/or ways of using the embodiments described herein are provided by way of example only and not limitation. Specific uses described herein are not provided to the exclusion of other uses unless the context expressly states otherwise.

Cardiac Electrophysiology

The electrical conduction system of the heart uses Nodal cells and Purkinje cells to maintain synchronization of the atria and the ventricle.

The electrical current is first initiated in the SA node, the hearts natural pacemaker, located at the top of the right atrium. The SA node is composed of nodal cells. In a normal resting adult heart, the SA node initiates firing at 60 to 100 impulses/minute, the impulses causing electrical stimulation and subsequent contraction of the atria. Located at the upper end of the septum, the sinus node creates the synchronized neurally-mediated signal for cardiac pacing.

These signals then travel across the atrium to the atrioventricular node, located close to the septal leaflet of the tricuspid valve. The AV node is also made up of nodal cells and coordinates these incoming electrical impulses.

After a slight delay so the atria can contract and complete ventricular filling, the AV node relays the impulse to Purkinje cells in the ventricle, initially conducted through the Bundle of His which extends along the septum, and which is then divided into the right bundle branch to conduct impulses to the right ventricle and the left bundle branch to conduct impulses to the left ventricle, causing ventricular contraction.

In a healthy heart, the signal flow from the A-V node to the free wall of the left ventricle is rapid to insure the free wall and septum contract in synchrony. For example, a stimulating signal may flow to the free wall in about 70-90 milli-seconds. In patients with conduction abnormalities, this timing may be significantly delayed (to 150 milli-seconds or more) resulting in asynchronous contraction.

In some patients, the conduction path through the Purkinje fibers may be blocked. The location of the block may be highly localized (as in the case of so-called “left bundle branch block” or LBBB) or may include an enlarged area of dysfunctional tissue (which can result from infarction). In such cases, all or a portion of the free wall of the left ventricle is flaccid while the septum is contracting. In addition to contributing to asynchronous contraction, the contraction force of the free wall is weakened.

To address asynchronous contraction, CHF patients can be treated with cardiac pacing of the left ventricle. Such pacing includes applying a stimulus to the septal muscles in synchrony with stimulation applied to the muscles of the free wall of the left ventricle. While infracted tissue will not respond to such stimulus, non-infarcted tissue will contract thereby heightening the output of the left ventricle.

FIGURES

Referring now to FIG. 1 is a schematic view of one embodiment of the device, illustrating the atrial leads, the ventricular leads, the retractable sheath, the combined hub and terminal connection, and steerable deployment mechanism, and the external lead terminals, according to the invention.

Referring now to FIG. 1, a distal central radio-opaque lead 101 is shown as one of a three-part set of ventricle leads. Ventricle leads 102 and 103 are shown bent at 90 degrees away from the central axis of lead 101, and are shown in a 180 degrees opposition position from each other

• • lead 102 is 180 degrees opposite lead 103 in the y-axial plane.

In a preferred embodiment, ventricle leads are formed from 0.010″ Nitinol. Lead 101 extends axially 6 cm from a distal radio-opaque band. Leads 102 and 103 bend away from the central lead and extend 4 cm away, each, from the central axis, respectively.

Atrium leads 104, 105, 106, 107 are bent 90 degrees extending away from the central axis, and are also bent 90 degrees from each other in the y-axis plane. Atrium leads extend 4 cm away, each, from the central axis, respectively.

Steerable catheter sheath is comprised of a distal portion 109 that is 5 cm in length and has a 0.010″ pitch coil. In a preferred embodiment, the distal portion is made from PebaSlix 35D. Steerable catheter sheath is also comprised of a proximal portion 113 that is 30 cm in length and has a 0.020″ pitch coil. In a preferred embodiment, the proximal portion is made from Pebax 72D. The sheath is configured to provide a 90 degree curve over a 2.5″ diameter bend, and is also configured to provide a hockey-stick bend at a 45 degree angle+/−5 degrees. Sheath has OS markers 110, 111, 112 located every 10 cm along its length from the distal tip 108.

At a proximal end, sheath has a glued hub 114, a Touhy-Borst access connector with a side port 115. Actuator dial 116 is located at the proximal end of the sheath and allows the sheath to be shaped and controlled. Red deployment stop 117 connects the last 20 cm 118 of the sheath to the cable junction housing 119.

Programmable Leads

Atrium lead terminals 120, 121 and ventricle lead terminals 122, 123 allow the device to be connected to and operated from an external unit such as a ICD, pacer, diagnostic, or other unit that can provide sensor operation, stimulation signal, programming for individual leads to improve sensing, avoid over-sensing of the ventricular lead by T-waves or other noise or attenuating or interfering signals, avoid over-sensing of the atrium leads by the R-wave, avoid cross-talk, or customize sensing and stimulation on a lead-by-lead basis.

Also contemplated as within the scope of the invention is the use digital signal processing in conjunction with the use of multiple leads. Multiple input, multiple output (MIMO), single input multiple output (SIMO), single input single output (SISO), and multiple input single output (MISO) can be programmed in the control unit to take advantage of the multiple lead architecture. For example, decreasing sensitivity of certain leads and increasing sensitivity of other leads during a depolarization cycle (PQRST) allows the invention to increase SNR in the sensing function. Similarly, decreasing or increasing stimulatory signals to one or more leads allows the invention to more accurately provide stimulation to the AV node, the SA node, the ventricular apex, or other cardiac tissue to provide a level of granularity to the stimulation function not previously available to practitioners. Likewise, unlike previous devices, the availability of multiple, programmable leads means that sensing leads are not required to share the function of a shocking/stimulation leads. Further, damaged or degraded leads can be bypassed allowing continued functioning without requiring the entire device to be removed from a patient, this increasing the longevity of implanted devices using the inventive technology.

As is customary with implantable pulse generators, the device may be programmable to achieve either conventional bipolar or unipolar stimulation or to achieve the stimulation of the present invention through an external programmer or controlled automatically by the device. The selection can be based on user preference or be driven by physiological factors such as widths of the patient's QRS complex or the conduction interval between the stimulus to a far away region in the heart. In addition switching between the pacing of the present invention and conventional pacing can also be determined by the percentage of pacing with a preference for a higher percentage with the pacing of the present invention. Further, the switching from the conventional pacing to the present invention pacing can be used when there exists an exit block or the pacing electrode is located in infracted myocardium when conventional pacing can not effect the depolarization of the myocardium at the high output level. The automatic determination can be effected through the deployment of any automatic capture detection technology that exists in the prior art. Additionally, wireless network enabled switching function for therapy optimization can also be implemented with the present invention. In such case, certain patient physiologic data are gathered by the implantable device and sent to a remote server/monitor through a wireless communication network.

The present invention can also be extended to the defibrillation therapy where high-energy pulses with various waveforms are delivered through electrode systems to treat tachycardia and fibrillation (both atrium and ventricle). The present invention is believed to be able to achieve lower defibrillation threshold due to better distribution of the electrical field, causing higher voltage gradient at least in certain parts of the heart compared to that by the conventional defibrillation configuration. Additionally, the present invention can be used to perform anti-tachy pacing where faster than conventional pacing pulse sequences are used to stop certain tachyarrhythmia. The present invention is believed to be advantageous due to the wider coverage of the electrical field and the capability of capturing special conductions system in the heart (both atrium and ventricle).

FIG. 2 is a schematic view another embodiment of the device, illustrating the atrial leads 104, 105, 106, 107, the ventricular leads 101, 102, 103, the retractable sheath 109, 113, the hub 114, the independent terminal connection 119, and steerable deployment mechanism 116, and the external lead terminals 120, 121, 122, 123, according to the invention. FIG. 2 also shows a 20 cm segment 118 from the deployment stop 117 and the terminal connection 119.

FIG. 3 is a schematic of the two-inner sheath embodiment illustrating the outer steerable catheter sheath 301 housing the two inner sheaths 302, 303, with one inner sheath 303 having the ventricle leads and the other inner sheath 302 having the atrium leads, according to the invention. Eyelet tip 305 is constructed with radiopaque material and configured/shaped, e.g. as a loop, to have a surface area larger than the point cross-section of a wire lead. In a preferred embodiment, the eyelet tip is 0.2-1.0 mm in area. Copper wire body portion 306 of the wire lead runs the length of the catheter from the pacemaker up to the distal shape memory portion 307. Shape memory portion 307 is attached to the copper wire 306 by bond, braid, weld, etc.

FIG. 4 is a schematic of the seven-inner sheath (multi-lumen) embodiment illustrating the outer steerable catheter sheath 401 housing the seven inner sheaths, with each inner sheath 404 having its own lead, and providing three (3) ventricle leads 403 and four (4) atrium leads 402, according to the invention. Eyelet tip 405 is constructed with radiopaque material and configured/shaped, e.g. as a loop, to have a surface area larger than the point cross-section of a wire lead. In a preferred embodiment, the eyelet tip is 0.2-1.0 mm in area. Copper wire body portion 406 of the wire lead runs the length of the catheter from the pacemaker up to the distal shape memory portion 407. Shape memory portion 407 is attached to the copper wire 406 by bond, braid, weld, etc.

FIG. 5 is a schematic of a cross-section of the seven-inner sheath (multi-lumen) embodiment 501 illustrating the outer steerable catheter sheath 501 housing the seven inner sheaths 502, 503, with each inner sheath its own lead, and providing three (3) ventricle leads and four (4) atrium leads, according to the invention.

Referring now to the FIG. 6, an external pacemaker 14 is shown connected to a bundle of insulated wire electrical conductors wrapped in a sheath 12. Specifically, the pacemaker 14 as shown is connected to a bundle of seven insulated conductive wires, three wires 20, 22, 26 of which are disposed within the ventricle and four wires 30, 32, 34, 36 of which are disposed in the atrium 28. The wires are bundled in a sheath 12 that was inserted into the ventricle and then pulled backward, exposing the three ventricle leads which are now contacting the walls of the ventricle due to the retained curved memory of each wire. As the sheath 12 is further withdrawn into the atrium, four additional electrodes 30, 32, 34, 36 are shown contacting atrial chamber 28 walls in accordance with the present invention.

As shown in the drawing, the invention as disclosed is a low profile transvenous electrode system for sequentially pacing both the atrium and ventricle of the heart in a dual chamber mode. As shown in the drawing, there are a plurality of insulated electrical wires represented that are electrical conductors and that are wrapped in electrical insulators. The wires are bundled together into two separate in-line sets of leads. Each wire has memory and is resilient. During manufacturing, each wire is pre-formed in a particular curvature and length so that when disposed within a heart chamber, atrium or ventricle, the electrode end of the wire will engage the chamber wall for electrical pulse transfer. In a preferred embodiment, the device comprises three (3) ventricular leads and four (4) atrial leads, made from shape memory material. Two of the three ventricular leads are bent at 90 degrees from the central axial lead and are 180 degrees from each other. The four atrial leads are bent at 90 degrees from the central axis (x-axis), and are each separated 90 degrees from the adjacent leads, in the y-axis plane.

Both sets of leads may also be mounted and contained inside a slender e.g. 8 Fr (8/3=2.66 mm), tubular, flexible elongated e.g. 35 cm retaining sheath that serves as a guide and delivery system during insertion and removal of the electrode system.

Each of the wires in the ventricle could be of different lengths with different shapes so that when the sheath is removed, each wire expands out by memory to have sufficient resiliency in distance to contact the inner wall of the ventricle as shown with the electrode points flush against the ventricle wall. There is a certain amount of resiliency in each wire holding the wire against the wall during pacing in the position as shown. The four wires used in the atrium are also pre-formed in curvature and length so that when the sheath is removed, wires expand resiliently against the walls of the atrium as shown in the drawing with electrode points disposed at the end of each wire against the wall tissue. The resiliency in each wire will hold the electrodes against the wall of the atrium while pacing.

The external pacemaker 14 provides the electrical pulses for the sequential pacing. The pacemaker 14 has two sequential pulse generators 16 and 18 which are connected to the proximal ends of the wires for providing the sequential pulses to both the ventricle through wires and to the atrium through wires. The external pacemaker itself is conventional in operation.

Pulse Generator

The term “pulse generator” is intended to include pacemakers, converter defibrillators and cardia resynchronization therapies (CRT), all known in the art.

It will be appreciated that the prior art contains numerous examples of cardiac leads for placement in a chamber of the heart, electrodes, attachment mechanisms, conductors and/or connector pins.

The pulse generator contains internal circuitry for creating electrical impulses which are applied to the electrodes after the lead is connected to the pulse generator. Also, such circuitry may include sensing and amplification circuitry so that electrodes may be used as sensing electrodes to sense and report on the patient's electrophysiology.

The lead may be introduced to the vasculature through a small incision and advanced through the vasculature and into the right atrium RA and right ventricle to the position. Such advancement typically occurs in an electrophysiology lab where the advancement of the lead can be visualized through fluoroscopy.

The pulse generator may contain a battery as a power supply.

The pulse generator circuitry controls the parameters of the signals coupled to the electrodes. These parameters can include pulse amplitude, timing, pulse duration by way of example. The internal circuitry further includes circuit logic permitting reprogramming of the pulse generator to permit a physician to alter pacing parameters to suit the need of a particular patient. Such programming can be affected by inputting programming instructions to the pulse generator via wireless transmission from an external programmer. Most commonly, the electrode is connected by the circuitry to an electrical ground.

In a preferred embodiment, the pulse generator may be external and coupled to the electrodes by percutaneous leads or wireless transmission.

Electrode Leads

The leads which are the wire conductors and electrodes are manufactured in different lengths and curved resiliently as discussed above with approximate distances between the electrodes to create a configuration or pattern as shown.

In a preferred embodiment, the leads are established inside the ventricle and established in the atrium.

The wires may have memory and with their pre-formed curvatures are resilient enough to be bundled in a small sheath prior to being mounted within the heart chambers. Both sets of wires may be contained inside a single, cylindrical, flexible retaining sheath that is the guide and delivery system during insertion and removal of the electrode system.

The ventricular electrodes may be pacemaker sensors or stimulators are released first after the retaining sheath has been successfully inserted into the right ventricle. The sheath may be retracted allowing the electrodes and wires to spread out and contact the endocardial surfaces. The wires expand outwardly as the sheath is removed engaging the tissue and chamber wall of the ventricle.

With a parallel configuration of wires is chosen, the wires can be released and make contact on the same plane within the ventricular chamber or they can be staggered.

The continued retraction of sheath may allow the escape of the atrial wires from the sheath which proceed toward the atrial tissue for engagement of the electrodes against the atrial wall.

Once the electrodes are disposed within the ventricular chamber and the atrium, sequential pacing can be initiated in the atrium and ventricle in a dual chamber mode providing an emergency pacemaker that will pace and sense both atrial and ventricular chambers and provide dual chamber control of the heart.

The dual chamber pacing refers to continuous monitoring of the spontaneous activity of the heart both in the atrial and in the ventricles interpreting the detective events according to certain accepted algorithms and providing stimuli to the chambers as needed to maintain a physiologically appropriate rhythm.

FIG. 7 is a chart of an acute first in human study and is useful to support an embodiment of the present invention. FIG. 7 shows an example study of a sample of 10 patients, although not necessarily for any specific indication. FIG. 7 shows that procedure time can average 24 minutes to position and deploy the device, pace the RV, pace the A synchronize AV pacing, perform a left side diagnostic, and the pace the RV, pace the A, synchronize the AV pacing, and remove the device.

FIG. 8 is an example of a chart of data in an embodiment of the invention from a procedure recording a non-limiting preferred embodiment. FIG. 8 shows by subject and lead, the impedance, the threshold, and the current, recorded. This shows safe delivery with and without fluoroscopic guidance, successful pacing, excellent contact and hold of the leads against the cardiac tissue, with no adverse events or significant adverse events at discharge.

FIGS. 9A, 9B, 9C is a sequence illustration of one embodiment. FIG. 9A shows a device being introduced into the jugular vein of a patient using a guidewire 901 and introducer 902. Luer 903 is shown connecting near hub 904, with outer delivery catheter 905 accessing down the jugular vein. FIG. 9B shows removal of the guidewire 901. FIG. 9C shows introduction of the transvenous dual-chamber sequential pacing device having steerable catheter sheath 906 into the deliver catheter 905.

FIG. 10 is an illustration of one embodiment of the transvenous dual-chamber sequential pacing device deployed into a heart using steerable catheter 906, as shown on fluoroscopic imaging.

FIG. 11 is an illustration of one embodiment of the transvenous dual-chamber sequential pacing device deployed into a heart using steerable catheter 906, as shown on fluoroscopic imaging.

FIG. 12 is an illustration of one embodiment of the transvenous dual-chamber sequential pacing device deployed into a heart using a steerable catheter 906, as shown in a cut-away view into the heart.

FIG. 13 is an illustration of one embodiment of the transvenous dual-chamber sequential pacing device deployed into a heart, with ventricle leads 907, 908, 909 deployed from a movable inner sheath into the ventricle.

FIG. 14 is an illustration of one embodiment of the transvenous dual-chamber sequential pacing device deployed into a heart, with atrium leads 910, 911, 912, 913 being deployed from a movable inner sheath into the atrium, while ventricle leads have already been deployed into the ventricle.

FIG. 15 is an illustration showing how the device can sense abnormal heart rhythm using the transvenous dual-chamber sequential pacing device deployed into a heart.

FIG. 16 is an illustration showing how the device can provide electrical stimulation to the atrium using the transvenous dual-chamber sequential pacing device deployed into a heart.

FIG. 17 is an illustration showing how the device can provide electrical stimulation to the ventricle using the transvenous dual-chamber sequential pacing device deployed into a heart.

FIG. 18 is an illustration showing how the device can sense the corrected normal heart rhythm using the transvenous dual-chamber sequential pacing device deployed into a heart.

FIG. 19 is an illustration showing how the device is removed after being deployed into a heart. Here, the leads may be removed by simply pulling, in one embodiment. In another embodiment, the sheath(s) may be re-introduced to gather the leads prior to removal.

FIG. 20 is an illustration of a ventricle only embodiment of the invention. FIG. 20 shows catheter 2001 having the unipolar leads 2002, 2003 disposed therein. The leads 2002, 2003 are shown having optional radiopaque insulating covering 2004 in a non-limiting embodiment. Conventional temporary pacemaker 2005 is attached to the leads by way of the brachial vein to provide dual ventricular leads in the right ventricle for pacing. In a non-limiting preferred embodiment, the catheter if 4 French in size, or 4/3 mm (1.33 mm) in diameter. Leads 2002, 2003 may include radiopaque eyelet tips, and may also include a proximal portion made of copper with a distal portion made from steel or nickel-titanium (NiTi) alloy, in a non-limiting embodiment as previously described.

Legal Equivalents

Many modifications and variations can be made without departing from its spirit and scope, as will be apparent to those skilled in the art. Functionally equivalent methods and apparatuses within the scope of the disclosure, in addition to those enumerated herein, will be apparent to those skilled in the art from the foregoing descriptions. Such modifications and variations are intended to fall within the scope of the appended claims. The present disclosure is to be limited only by the terms of the appended claims, along with the full scope of equivalents to which such claims are entitled. It is to be understood that this disclosure is not limited to particular methods, reagents, compounds, compositions or biological systems, which can, of course, vary. It is also to be understood that the terminology used herein is for the purpose of describing particular embodiments only, and is not intended to be limiting.

While various embodiments have been described above, it should be understood that they have been presented by way of example only, and not limitation. Where methods described above indicate certain events occurring in certain order, the ordering of certain events may be modified. Additionally, certain of the events may be performed concurrently in a parallel process when possible, as well as performed sequentially as described above.

Where schematics and/or embodiments described above indicate certain components arranged in certain orientations or positions, the arrangement of components may be modified. While the embodiments have been particularly shown and described, it will be understood that various changes in form and details may be made. Any portion of the apparatus and/or methods described herein may be combined in any combination, except mutually exclusive combinations.

The embodiments described herein can include various combinations and/or sub-combinations of the functions, components, and/or features of the different embodiments described. Various of the above-disclosed and other features and functions, or alternatives thereof, may be combined into many other different systems or applications. Various presently unforeseen or unanticipated alternatives, modifications, variations, or improvements therein may be subsequently made by those skilled in the art, each of which is also intended to be encompassed by the disclosed embodiments.

Claims

1. An electrode system connectable to a pacemaker for sequentially pacing both the atrium and ventricle of a human heart comprising: a plurality of insulated electrical leads comprising a first set of three ventricle leads and a second set of four atrium leads, a ventricular sheath over the ventricle leads and an atrial sheath over the atrium leads, the ventricular sheath and the atrial sheath disposed inside an outer catheter sheaththe ventricular sheath being retractable from the ventricle leads to deploy the ventricle leads in the ventricle, each of the three ventricle leads having a resiliency and shape to be deployed in contact with the ventricle when the ventricular sheath is retracted therefrom,the atrial sheath being retractable from the atrium leads to deploy the atrium leads in the atrium, each of the four atrium leads having the resiliency and shape to be deployed in contact with the atrium when the sheath is retracted therefromthe atrium and ventricle leads being capable of both stimulating and sensing the ventricle and atrium and capable of providing dual chamber control of the heart,wherein the outer catheter sheath has a distal portion and a proximal portion, the proximal portion of the outer catheter sheath having a Tuohy-Borst access connector, a deployment stop, and a terminal connection for the leads.

2. A method for quickly deploying a cardiac pacing device to a heart in a patient, comprising: (i) Providing the electrode system in claim 1;(ii) Accessing a jugular vein in the patient and advancing the catheter sheath under ultrasound or other non-fluoroscopic imaging modality to the heart of the patient;(iii) Advancing the ventricular sheath to the ventricle, and withdrawing the ventricular sheath Withdrawing the outer catheter sheath to a first position to deploy the first set of three ventricle leads;(iv) Advancing the atrial sheath to the atrium, and withdrawing the atrial sheath to a second position to deploy the four atrium leads;(v) Performing a diagnostic test using the three ventricle leads and the four atrium leads to identify the patient cardiac patterns and to validate the operation of the system;(vi) Performing a cardiac pacing routine appropriate as a treatment for the patient cardiac pattern using the system .

3. The method of claim 2, wherein performing steps (i)-(iv) are performed in a time period no longer than 60 minutes.

4. The method of claim 2, wherein performing steps (i)-(iv) are performed in a time period no longer than 30 minutes.

5. The electrode system of claim 1 wherein each of said ventricle leads and each of said atrium leads has an individual inner sheath.

6. The electrode system of claim 1 wherein each of said leads has a proximal portion made from wire with radio opaque insulation and a distal portion made from shape memory material.

7. The electrode system of claim 6 wherein each of said leads has a radio opaque tip.

8. The electrode system of claim 1, wherein when deployed in the ventricle, one of said ventricle leads is central axial lead and two ventricle leads are shape-set at 90 degrees to the central axial lead and are offset 180 degrees from each other in a plane perpendicular to the central axial lead.

9. The electrode system of claim 8 wherein, when connected to a pacemaker, the central axial lead and a second ventricle lead has a signal of a first polarity, and the third ventricle lead has a signal of an opposite polarity.

10. The electrode system of claim 8 wherein, when the atrium leads are deployed in the atrium, the atrium leads are shape-set at 90 degrees to the central axial lead and offset 90 degrees from each other in a plane perpendicular to the central axial lead.

11. The electrode system of claim 10 wherein, when connected to a pacemaker, two of the atrium leads have a signal of a first polarity and two of the atrium leads have a signal of an opposite polarity.

12. The electrode system of claim 1 where the atrium leads have different lengths.

13. The electrode system of claim 12 whereby the different lengths prevent entanglement of the atrium leads upon deployment in the atrium.

14. The electrode system of claim 1 wherein the outer catheter sheath has a segment between the deployment stop and the terminal connection.

15. The electrode system of claim 1 wherein, upon deployment of the outer catheter sheath in a blood vessel, the segment remains outside the blood vessel.

16. The electrode system of claim 1 wherein the outer catheter sheath has a bend.

17. The electrode system of claim 16 wherein the bend is a curved 90 degree bend.

18. The electrode system of claim 16 wherein the bend is 45 degrees.

19. A method for synchronous pacing of an atrium and a ventricle of a human heart comprising the steps of: inserting the electrode system of claim 1 into a blood vessel,guiding the catheter sheath of the electrode system into or near the heart, advancing the ventricular sheath to the ventricle, andin a first retracting step, retracting the ventricular sheath to enable the ventricle leads to escape from the ventricular sheath and contact the walls of the ventricle, and advancing the atrial sheath to the atrium, andin a second retracting step, retracting the atrial sheath to enable the atrium leads to escape from the atrial sheath and contact the atrium, and synchronously pacing the ventricle and atrium using a pacemaker connected to the ventricle leads and atrium leads.

20. The method of claim 19 further comprising the step of detecting contact of the ventricle leads with the ventricle wall using the pacemaker connected to the ventricle leads.

21. The method of claim 19 further comprising the step of detecting contact of the atrium leads with the atrium using the pacemaker connected to the atrium leads.