US20020035378A1

US20020035378A1 - Subcutaneous electrode for transthoracic conduction with highly maneuverable insertion tool

Info

Publication number: US20020035378A1
Application number: US09/940,356
Authority: US
Inventors: Gust Bardy; Riccardo Cappato; William Rissmann; Gary Sanders
Original assignee: Cameron Health Inc
Current assignee: Cameron Health Inc
Priority date: 2000-09-18
Filing date: 2001-08-27
Publication date: 2002-03-21

Abstract

One embodiment of the present invention provides a lead electrode assembly for subcutaneous implantation including an electrode; at least two channel guides coupled to the electrode for positioning the lead electrode assembly.

Description

CROSS-REFERENCE TO RELATED APPLICATIONS

The present application is a continuation-in-part of U.S. patent application entitled “SUBCUTANEOUS ONLY IMPLANTABLE CARDIOVERTER-DEFIBRILLATOR AND OPTIONAL PACER,” having Ser. No. 09/663,606, filed Sep. 18, 2000, pending, and U.S. patent application entitled “UNITARY SUBCUTANEOUS ONLY IMPLANTABLE CARDIOVERTER-DEFIBRILLATOR AND OPTIONAL PACER,” having Ser. No. 09/663,607, filed Sep. 18, 2000, pending, of which both applications are assigned to the assignee of the present application, and the disclosures of both applications are hereby incorporated by reference. [0001]
In addition, the present application is filed concurrently herewith U.S. patent application entitled “DUCKBILL-SHAPED IMPLANTABLE CARDIOVERTER-DEFIBRILLATOR AND METHOD OF USE,” U.S. patent application entitled “CERAMICS AND/OR OTHER MATERIAL INSULATED SHELL FOR ACTIVE AND NON-ACTIVE S-ICD CAN,” U.S. patent application entitled “SUBCUTANEOUS ELECTRODE FOR TRANSTHORACIC CONDUCTION WITH IMPROVED INSTALLATION CHARACTERISTICS,” U.S. patent application entitled “SUBCUTANEOUS ELECTRODE WITH IMPROVED CONTACT SHAPE FOR TRANSTHORACIC CONDUCTION,” U.S. patent application entitled “SUBCUTANEOUS ELECTRODE FOR TRANSTHORACIC CONDUCTION WITH LOW-PROFILE INSTALLATION APPENDAGE AND METHOD OF DOING SAME,” U.S. patent application entitled “SUBCUTANEOUS ELECTRODE FOR TRANSTHORACIC CONDUCTION WITH INSERTION TOOL,” U.S. patent application entitled “METHOD OF INSERTION AND IMPLANTATION FOR IMPLANTABLE CARDIOVERTER-DEFIBRILLATOR CANISTERS,” U.S. patent application entitled “CANISTER DESIGNS FOR IMPLANTABLE CARDIOVERTER-DEFIBRILLATORS,” U.S. patent application entitled “RADIAN CURVED IMPLANTABLE CARDIOVERTER-DEFIBRILLATOR CANISTER,” U.S. patent application entitled “CARDIOVERTER-DEFIBRILLATOR HAVING A FOCUSED SHOCKING AREA AND ORIENTATION THEREOF,” U.S. patent application entitled “BIPHASIC WAVEFORM FOR ANTI-BRADYCARDIA PACING FOR A SUBCUTANEOUS IMPLANTABLE CARDIOVERTER-DEFIBRILLATOR,” U.S. patent application entitled “BIPHASIC WAVEFORM FOR ANTI-TACHYCARDIA PACING FOR A SUBCUTANEOUS IMPLANTABLE CARDIOVERTER-DEFIBRILLATOR,” and U.S. patent application entitled “POWER SUPPLY FOR A SUBCUTANEOUS IMPLANTABLE CARDIOVERTER-DEFIBRILLATOR,” the disclosures of which applications are hereby incorporated by reference.[0002]

FIELD OF THE INVENTION

The present invention relates to an apparatus and method for performing electrical cardioversion/defibrillation and optional pacing of the heart via a totally subcutaneous nontransvenous system.

BACKGROUND OF THE INVENTION

Defibrillation/cardioversion is a technique employed to counter arrhythmic heart conditions including some tachycardias in the atria and/or ventricles. Typically, electrodes are employed to stimulate the heart with electrical impulses or shocks, of a magnitude substantially greater than pulses used in cardiac pacing.

Defibrillation/cardioversion systems include body implantable electrodes and are referred to as implantable cardioverter/defibrillators (ICDs). Such electrodes can be in the form of patches applied directly to epicardial tissue, or at the distal end regions of intravascular catheters, inserted into a selected cardiac chamber. U.S. Pat. Nos. 4,603,705, 4,693,253, 4,944,300, 5,105,810, the disclosures of which are all incorporated herein by reference, disclose intravascular or transvenous electrodes, employed either alone or in combination with an epicardial patch electrode. Compliant epicardial defibrillator electrodes are disclosed in U.S. Pat. Nos. 4,567,900 and 5,618,287, the disclosures of which are incorporated herein by reference. A sensing epicardial electrode configuration is disclosed in U.S. Pat. No. 5,476,503, the disclosure of which is incorporated herein by reference.

In addition to epicardial and transvenous electrodes, subcutaneous electrode systems have also been developed. For example, U.S. Pat. Nos. 5,342,407 and 5,603,732, the disclosures of which are incorporated herein by reference, teach the use of a pulse monitor/generator surgically implanted into the abdomen and subcutaneous electrodes implanted in the thorax. This system is far more complicated to use than current ICD systems using transvenous lead systems together with an active can electrode and therefore it has o practical use. It has in fact never been used because of the surgical difficulty of applying such a device (3 incisions), the impractical abdominal location of the generator and the electrically poor sensing and defibrillation aspects of such a system.

Recent efforts to improve the efficiency of ICDs have led manufacturers to produce ICDs which are small enough to be implanted in the pectoral region. In addition, advances in circuit design have enabled the housing of the ICD to form a subcutaneous electrode. Some examples of ICDs in which the housing of the ICD serves as an optional additional electrode are described in U.S. Pat. Nos. 5,133,353, 5,261,400, 5,620,477, and 5,658,321 the disclosures of which are incorporated herein by reference.

ICDs are now an established therapy for the management of life threatening cardiac rhythm disorders, primarily ventricular fibrillation (V-Fib). ICDs are very effective at treating V-Fib, but are therapies that still require significant surgery.

As ICD therapy becomes more prophylactic in nature and used in progressively less ill individuals, especially children at risk of cardiac arrest, the requirement of ICD therapy to use intravenous catheters and transvenous leads is an impediment to very long term management as most individuals will begin to develop complications related to lead system malfunction sometime in the 5-10 year time frame, often earlier. In addition, chronic transvenous lead systems, their reimplantation and removals, can damage major cardiovascular venous systems and the tricuspid valve, as well as result in life threatening perforations of the great vessels and heart. Consequently, use of transvenous lead systems, despite their many advantages, are not without their chronic patient management limitations in those with life expectancies of >5 years. The problem of lead complications is even greater in children where body growth can substantially alter transvenous lead function and lead to additional cardiovascular problems and revisions. Moreover, transvenous ICD systems also increase cost and require specialized interventional rooms and equipment as well as special skill for insertion. These systems are typically implanted by cardiac electrophysiologists who have had a great deal of extra training.

In addition to the background related to ICD therapy, the present invention requires a brief understanding of automatic external defibrillator (AED) therapy. AEDs employ the use of cutaneous patch electrodes to effect defibrillation under the direction of a bystander user who treats the patient suffering from V-Fib. AEDs can be as effective as an ICD if applied to the victim promptly within 2 to 3 minutes.

AED therapy has great appeal as a tool for diminishing the risk of death in public venues such as in air flight. However, an AED must be used by another individual, not the person suffering from the potential fatal rhythm. It is more of a public health tool than a patient-specific tool like an ICD. Because >75% of cardiac arrests occur in the home, and over half occur in the bedroom, patients at risk of cardiac arrest are often alone or asleep and can not be helped in time with an AED. Moreover, its success depends to a reasonable degree on an acceptable level of skill and calm by the bystander user.

What is needed therefore, especially for children and for prophylactic long term use, is a combination of the two forms of therapy which would provide prompt and near-certain defibrillation, like an ICD, but without the long-term adverse sequelae of a transvenous lead system while simultaneously using most of the simpler and lower cost technology of an AED. What is also needed is a cardioverter/defibrillator that is of simple design and can be comfortably implanted in a patient for many years.

SUMMARY OF THE INVENTION

BRIEF DESCRIPTION OF THE DRAWINGS

For a better understanding of the invention, reference is now made to the drawings where like numerals represent similar objects throughout the figures where: [0014]
FIG. 1 is a schematic view of a Subcutaneous ICD (S-ICD) of the present invention; [0015]
FIG. 2 is a schematic view of an alternate embodiment of a subcutaneous electrode of the present invention; [0016]
FIG. 3 is a schematic view of an alternate embodiment of a subcutaneous electrode of the present invention; [0017]
FIG. 4 is a schematic view of the S-ICD and lead of FIG. 1 subcutaneously implanted in the thorax of a patient; [0018]
FIG. 5 is a schematic view of the S-ICD and lead of FIG. 2 subcutaneously implanted in an alternate location within the thorax of a patient; [0019]
FIG. 6 is a schematic view of the S-ICD and lead of FIG. 3 subcutaneously implanted in the thorax of a patient; [0020]
FIG. 7 is a schematic view of the method of making a subcutaneous path from the preferred incision and housing implantation point to a termination point for locating a subcutaneous electrode of the present invention; [0021]
FIG. 8 is a schematic view of an introducer set for performing the method of lead insertion of any of the described embodiments; [0022]
FIG. 9 is a schematic view of an alternative S-ICD of the present invention illustrating a lead subcutaneously and serpiginously implanted in the thorax of a patient for use particularly in children; [0023]
FIG. 10 is a schematic view of an alternate embodiment of an S-ICD of the present invention; [0024]
FIG. 11 is a schematic view of the S-ICD of FIG. 10 subcutaneously implanted in the thorax of a patient; [0025]
FIG. 12 is a schematic view of yet a further embodiment where the canister of the S-ICD of the present invention is shaped to be particularly useful in placing subcutaneously adjacent and parallel to a rib of a patient; and [0026]
FIG. 13 is a schematic of a different embodiment where the canister of the S-ICD of the present invention is shaped to be particularly useful in placing subcutaneously adjacent and parallel to a rib of a patient. [0027]
FIG. 14 is a schematic view of a Unitary Subcutaneous ICD (US-ICD) of the present invention; [0028]
FIG. 15 is a schematic view of the US-ICD subcutaneously implanted in the thorax of a patient; [0029]
FIG. 16 is a schematic view of the method of making a subcutaneous path from the preferred incision for implanting the US-ICD. [0030]
FIG. 17 is a schematic view of an introducer for performing the method of US-ICD implantation; and [0031]
FIG. 18 is an exploded schematic view of an alternate embodiment of the present invention with a plug-in portion that contains operational circuitry and means for generating cardioversion/defibrillation shock waves. [0032]
FIG. 14([0033] a) is a side plan view of an embodiment of a lead electrode assembly with a top-mounted fin;
FIG. 14([0034] b) is a top plan view of an embodiment of a lead electrode assembly with a top-mounted fin;
FIG. 14([0035] c) is a side plan view of a section of the lead in an embodiment of the lead electrode assembly;
FIG. 14([0036] d) is a cross-sectional view of a filar in the lead in an embodiment of the lead electrode assembly;
FIG. 14([0037] e) is a cross-sectional view of the lead fastener of an embodiment of a lead electrode assembly;
FIG. 14([0038] f) is an exploded view of the lead fastener of an embodiment of a lead electrode assembly;
FIG. 15([0039] a) is a cross-sectional front plan view of an embodiment of a lead electrode assembly with a top-mounted fin;
FIG. 15([0040] b) is a top plan view of an embodiment of a lead electrode assembly with a top-mounted fin;
FIG. 16([0041] a) is a perspective view of an embodiment of a lead electrode assembly with a top-mounted fin;
FIG. 17([0042] a) is a cross-sectional side plan view of an embodiment of a lead electrode assembly with a top-mounted fin and a molded cover;
FIG. 17([0043] b) is a cross-sectional side plan view of an embodiment of a lead electrode assembly with a top-mounted fin that is slope-shaped and a molded cover;
FIG. 17([0044] c) is cross-sectional front plan view of an embodiment of a lead electrode assembly with a top-mounted fin and a molded cover;
FIG. 17([0045] d) is an exploded top plan view of the lead fastener in an embodiment of a lead electrode assembly with a top-mounted fin and a molded cover;
FIG. 17([0046] e) is a bottom plan view of an embodiment of a lead electrode assembly with a top-mounted fin and a molded cover;
FIG. 17([0047] f) is a side plan view of an embodiment of a lead electrode assembly with a top-mounted fin and a molded cover;
FIG. 17([0048] g) is a top plan view of an embodiment of a lead electrode assembly with a top-mounted fin and a molded cover;
FIG. 18([0049] a) is a side plan view of an embodiment of a lead electrode assembly with an elongated top-mounted fin and a molded cover;
FIG. 18([0050] b) is a top plan view of an embodiment of a lead electrode assembly with an elongated top-mounted fin and a molded cover;
FIG. 18([0051] c) is a bottom plan view of an embodiment of a lead electrode assembly with an elongated top-mounted fin and a molded cover;
FIG. 19 is a side plan view of a lead electrode assembly demonstrating the curvature of the electrode; [0052]
FIG. 20([0053] a) is a top plan view of the backing layer and electrode of an embodiment of a lead electrode assembly with a side-mounted fin;
FIG. 20([0054] b) is a side plan view of the backing layer and electrode of an embodiment of a lead electrode assembly with a side-mounted fin;
FIG. 20([0055] c) is a bottom plan view of an embodiment of a lead electrode assembly with a side-mounted fin;
FIG. 20([0056] d) is a bottom plan view of an embodiment of a lead electrode assembly with a side-mounted fin with a slope-shape;
FIG. 21([0057] a) is a side plan view of a lead electrode assembly with a top-mounted loop;
FIG. 21([0058] b) is a cross-sectional rear plan view of a lead electrode assembly with a top-mounted loop;
FIG. 21([0059] c) is a top plan view of a lead electrode assembly with a top-mounted loop;
FIG. 22([0060] a) is a top plan view of a backing layer for use in an embodiment of a lead electrode assembly with a top-mounted fin formed as part of the backing layer;
FIG. 22([0061] b) is a top plan view of an embodiment of a lead electrode assembly with a top-mounted fin formed as part of the backing layer;
FIG. 22([0062] c) is a side plan view of an embodiment of a lead electrode assembly with a top-mounted fin formed as part of the backing layer;
FIG. 22([0063] d) is a front plan view of an embodiment of a lead electrode assembly with a top-mounted fin formed as part of a backing layer;
FIG. 22([0064] e) is a side plan view of an embodiment of a lead electrode assembly with a top-mounted fin formed as part of a two-piece backing layer;
FIG. 22([0065] f) is a front plan view of an embodiment of a lead electrode assembly with a top-mounted fin formed as part of a two-piece backing layer;
FIG. 23([0066] a) is a front plan view of the embodiment of the lead electrode assembly of FIGS. 22(e) and (f) in an upright position;
FIG. 23([0067] b) is a front plan view of the embodiment of the lead electrode assembly of FIGS. 22(e) and (f) illustrating the ability of the fin to fold;
FIG. 24([0068] a) is a front plan view of an embodiment of a lead electrode assembly with a top-mounted tube formed as part of a backing layer;
FIG. 24([0069] b) is a side plan view of an embodiment of a lead electrode assembly with a top-mounted tube formed as part of a backing layer;
FIG. 24([0070] c) is a top plan view of an embodiment of a lead electrode assembly with a top-mounted tube formed as part of a backing layer;
FIG. 25([0071] a) is a front plan view of an embodiment of a lead electrode assembly with a top-mounted fin connected with flexible joining material in an upright position;
FIG. 25([0072] b) is a front plan view of an embodiment of a lead electrode assembly with a top-mounted fin connected with flexible joining material in a folded position;
FIG. 25([0073] c) is a top plan view of an embodiment of a lead electrode assembly with a top-mounted fin connected with flexible joining material in an upright position;
FIG. 26 is a perspective view of an embodiment of a lead electrode assembly in which the appendage is a cylindrical tube; [0074]
FIG. 27 is a perspective view of an embodiment of a lead electrode assembly in which the appendage is a tube with a substantially triangular cross section; [0075]
FIGS. [0076] 28(a)-(d) are top plan views of embodiments of lead electrode assemblies illustrating shapes of the electrode and the lines of the lead;
FIGS. [0077] 28(e)-(h) are bottom plan views of embodiments of lead electrode assemblies illustrating shapes of the electrode;
FIG. 29 is a perspective view of a custom hemostat for lead electrode assembly implantation; [0078]
FIG. 30([0079] a) is a perspective view of a patient's ribcage showing the orientation of the components in an implanted S-ICD system;
FIG. 30([0080] b) is a cross-sectional side plan view of a patient's rib cage, skin, fat and the lead of the lead electrode assembly;
FIG. 31 is a front plan view illustrating the incision point for the surgery to implant the lead electrode assembly; [0081]
FIG. 32([0082] a) is a cross-sectional bottom plan view of a patient along line 32(a) of FIG. 31 illustrating the creation of a subcutaneous path for implantation of the lead electrode assembly of an S-ICD system;
FIG. 32([0083] b) is a perspective view of a lead electrode assembly captured by a custom hemostat;
FIG. 32([0084] c) is a cross-sectional bottom plan view of a patient along line 32(a) of FIG. 31 illustrating the implantation of a lead electrode assembly via the subcutaneous path;
FIG. 32([0085] d) is a top view of a lead electrode assembly captured by a custom hemostat;
FIG. 33([0086] a) is a perspective view of a rail of an embodiment of the lead electrode assembly;
FIG. 33([0087] b) is a cross-sectional front plan view of an embodiment of the lead electrode assembly where the appendage is a rail;
FIG. 33([0088] c) is a top plan view of an embodiment of the lead electrode assembly where the appendage is a rail;
FIG. 34 is a top view of an embodiment of the lead electrode assembly where the appendage is a rail; [0089]
FIG. 35([0090] a) is a perspective view of a lead electrode assembly manipulation tool with a rail fork;
FIG. 35([0091] b) is a top plan view of a lead electrode assembly manipulation tool with a rail fork;
FIG. 35([0092] c) is a side plan view of a lead electrode assembly manipulation tool with a rail fork;
FIG. 35([0093] d) is a top plan view of a lead electrode assembly having a rail captured by a lead electrode assembly manipulation tool with a rail fork;
FIG. 36([0094] a) is a cross-sectional side plan view of a lead electrode assembly with a pocket;
FIG. 36([0095] b) is a top plan view of a lead electrode assembly with a pocket;
FIG. 36([0096] c) is a cross-sectional side plan view of a lead electrode assembly with a pocket and a fin;
FIG. 37([0097] a) is a bottom plan view of a lead electrode assembly with a pocket;
FIG. 37([0098] b) is a top plan view of a lead electrode assembly with a pocket;
FIG. 38([0099] a) is a top plan view of a lead electrode assembly manipulation tool with a paddle;
FIG. 38([0100] b) is a side plan view of a lead electrode assembly manipulation tool with a paddle;
FIG. 38([0101] c) is a top plan view of a lead electrode assembly with a pocket captured by a lead electrode assembly manipulation tool with a paddle;
FIG. 39([0102] a) is a cross-sectional rear plan view of a lead electrode assembly with a first channel guide and a second channel guide;
FIG. 39([0103] b) is a top plan view of a lead electrode assembly with a first channel guide and a second channel guide;
FIG. 40([0104] a) is a top plan view of a lead electrode assembly manipulation tool with a channel guide fork;
FIG. 40([0105] b) is a top plan view of a lead electrode assembly with a first channel guide and a second channel guide captured by a lead electrode assembly manipulation tool with a channel guide fork;
FIG. 41([0106] a) is a perspective view of a subcutaneous implantable cardioverter-defibrillator kit; and
FIG. 41([0107] b) is a perspective view of a hemostat illustrating the length measurement.

DETAILED DESCRIPTION

Turning now to FIG. 1, the S-ICD of the present invention is illustrated. The S-ICD consists of an electrically [0108] active canister 11 and a subcutaneous electrode 13 attached to the canister. The canister has an electrically active surface 15 that is electrically insulated from the electrode connector block 17 and the canister housing 16 via insulating area 14. The canister can be similar to numerous electrically active canisters commercially available in that the canister will contain a battery supply, capacitor and operational circuitry. Alternatively, the canister can be thin and elongated to conform to the intercostal space. The circuitry will be able to monitor cardiac rhythms for tachycardia and fibrillation, and if detected, will initiate charging the capacitor and then delivering cardioversion/defibrillation energy through the active surface of the housing and to the subcutaneous electrode. Examples of such circuitry are described in U.S. Pat. Nos. 4,693,253 and 5,105,810, the entire disclosures of which are herein incorporated by reference. The canister circuitry can provide cardioversion/defibrillation energy in different types of waveforms. In the preferred embodiment, a 100 uF biphasic waveform is used of approximately 10-20 ms total duration and with the initial phase containing approximately {fraction (2/3)} of the energy, however, any type of waveform can be utilized such as monophasic, biphasic, multiphasic or alternative waveforms as is known in the art.
In addition to providing cardioversion/defibrillation energy, the circuitry can also provide transthoracic cardiac pacing energy. The optional circuitry will be able to monitor the heart for bradycardia and/or tachycardia rhythms. Once a bradycardia or tachycardia rhythm is detected, the circuitry can then deliver appropriate pacing energy at appropriate intervals through the active surface and the subcutaneous electrode. Pacing stimuli will be biphasic in the preferred embodiment and similar in pulse amplitude to that used for conventional transthoracic pacing. [0109]
This same circuitry can also be used to deliver low amplitude shocks on the T-wave for induction of ventricular fibrillation for testing S-ICD performance in treating V-Fib as is described in U.S. Pat. No. 5,129,392, the entire disclosure of which is hereby incorporated by reference. Also the circuitry can be provided with rapid induction of ventricular fibrillation or ventricular tachycardia using rapid ventricular pacing. Another optional way for inducing ventricular fibrillation would be to provide a continuous low voltage, i.e., about 3 volts, across the heart during the entire cardiac cycle. [0110]
Another optional aspect of the present invention is that the operational circuitry can detect the presence of atrial fibrillation as described in Olson, W. et al. “Onset And Stability For Ventricular Tachyarrhythmia Detection in an Implantable Cardioverter and Defibrillator,” Computers in Cardiology (1986) pp. 167-170. Detection can be provided via RR Cycle length instability detection algorithms. Once atrial fibrillation has been detected, the operational circuitry will then provide QRS synchronized atrial defibrillation/cardioversion using the same shock energy and waveshape characteristics used for ventricular defibrillation/cardioversion. [0111]
The sensing circuitry will utilize the electronic signals generated from the heart and will primarily detect QRS waves. In one embodiment, the circuitry will be programmed to detect only ventricular tachycardias or fibrillations. The detection circuitry will utilize in its most direct form, a rate detection algorithm that triggers charging of the capacitor once the ventricular rate exceeds some predetermined level for a fixed period of time: for example, if the ventricular rate exceeds 240 bpm on average for more than 4 seconds. Once the capacitor is charged, a confirmatory rhythm check would ensure that the rate persists for at least another 1 second before discharge. Similarly, termination algorithms could be instituted that ensure that a rhythm less than 240 bpm persisting for at least 4 seconds before the capacitor charge is drained to an internal resistor. Detection, confirmation and termination algorithms as are described above and in the art can be modulated to increase sensitivity and specificity by examining QRS beat-to-beat uniformity, QRS signal frequency content, R-R interval stability data, and signal amplitude characteristics all or part of which can be used to increase or decrease both sensitivity and specificity of S-ICD arrhythmia detection function. [0112]
In addition to use of the sense circuitry for detection of V-Fib or V-Tach by examining the QRS waves, the sense circuitry can check for the presence or the absence of respiration. The respiration rate can be detected by monitoring the impedance across the thorax using subthreshold currents delivered across the active can and the high voltage subcutaneous lead electrode and monitoring the frequency in undulation in the waveform that results from the undulations of transthoracic impedance during the respiratory cycle. If there is no undulation, then the patent is not respiring and this lack of respiration can be used to confirm the QRS findings of cardiac arrest. The same technique can be used to provide information about the respiratory rate or estimate cardiac output as described in U.S. Pat. Nos. 6,095,987, 5,423,326, 4,450,527, the entire disclosures of which are incorporated herein by reference. [0113]
The canister of the present invention can be made out of titanium alloy or other presently preferred electrically active canister designs. However, it is contemplated that a malleable canister that can conform to the curvature of the patient's chest will be preferred. In this way the patient can have a comfortable canister that conforms to the shape of the patient's rib cage. Examples of conforming canisters are provided in U.S. Pat. No. 5,645,586, the entire disclosure of which is herein incorporated by reference. Therefore, the canister can be made out of numerous materials such as medical grade plastics, metals, and alloys. In the preferred embodiment, the canister is smaller than 60 cc volume having a weight of less than 100 gms for long term wearability, especially in children. The canister and the lead of the S-ICD can also use fractal or wrinkled surfaces to increase surface area to improve defibrillation capability. Because of the primary prevention role of the therapy and the likely need to reach energies over 40 Joules, a feature of the preferred embodiment is that the charge time for the therapy, intentionally e relatively long to allow capacitor charging within the limitations of device size. Examples of small ICD housings are disclosed in U.S. Pat. Nos. 5,597,956 and 5,405,363, the entire disclosures of which are herein incorporated by reference. [0114]
Different [0115] subcutaneous electrodes 13 of the present invention are illustrated in FIGS. 1-3. Turning to FIG. 1, the lead 21 for the subcutaneous electrode is preferably composed of silicone or polyurethane insulation. The electrode is connected to the canister at its proximal end via connection port 19 which is located on an electrically insulated area 17 of the canister. The electrode illustrated is a composite electrode with three different electrodes attached to the lead. In the embodiment illustrated, an optional anchor segment 52 is attached at the most distal end of the subcutaneous electrode for anchoring the electrode into soft tissue such that the electrode does not dislodge after implantation.
The most distal electrode on the composite subcutaneous electrode is a [0116] coil electrode 27 that is used for delivering the high voltage cardioversion/defibrillation energy across the heart. The coil cardioversion/defibrillation electrode is about 5-10 cm in length. Proximal to the coil electrode are two sense electrodes, a first sense electrode 25 is located proximally to the coil electrode and a second sense electrode 23 is located proximally to the first sense electrode. The sense electrodes are spaced far enough apart to be able to have good QRS detection. This spacing can range from 1 to 10 cm with 4 cm being presently preferred. The electrodes may or may not be circumferential with the preferred embodiment. Having the electrodes non-circumferential and positioned outward, toward the skin surface, is a means to minimize muscle artifact and enhance QRS signal quality. The sensing electrodes are electrically isolated from the cardioversion/defibrillation electrode via insulating areas 29. Similar types of cardioversion/defibrillation electrodes are currently commercially available in a transvenous configuration. For example, U.S. Pat. No. 5,534,022, the entire disclosure of which is herein incorporated by reference, disclosures a composite electrode with a coil cardioversion/defibrillation electrode and sense electrodes. Modifications to this arrangement is contemplated within the scope of the invention. One such modification is illustrated in FIG. 2 where the two sensing electrodes 25 and 23 are non-circumferential sensing electrodes and one is located at the distal end, the other is located proximal thereto with the coil electrode located in between the two sensing electrodes. In this embodiment the sense electrodes are spaced about 6 to about 12 cm apart depending on the length of the coil electrode used. FIG. 3 illustrates yet a further embodiment where the two sensing electrodes are located at the distal end to the composite electrode with the coil electrode located proximally thereto. Other possibilities exist and are contemplated within the present invention. For example, having only one sensing electrode, either proximal or distal to the coil cardioversion/defibrillation electrode with the coil serving as both a sensing electrode and a cardioversion/defibrillation electrode.
It is also contemplated within the scope of the invention that the sensing of QRS waves (and transthoracic impedance) can be carried out via sense electrodes on the canister housing or in combination with the cardioversion/defibrillation coil electrode and/or the subcutaneous lead sensing electrode(s). In this way, sensing could be performed via the one coil electrode located on the subcutaneous electrode and the active surface on the canister housing. Another possibility would be to have only one sense electrode located on the subcutaneous electrode and the sensing would be performed by that one electrode and either the coil electrode on the subcutaneous electrode or by the active surface of the canister. The use of sensing electrodes on the canister would eliminate the need for sensing electrodes on the subcutaneous electrode. It is also contemplated that the subcutaneous electrode would be provided with at least one sense electrode, the canister with at least one sense electrode, and if multiple sense electrodes are used on either the subcutaneous electrode and/or the canister, that the best QRS wave detection combination will be identified when the S-ICD is implanted and this combination can be selected, activating the best sensing arrangement from all the existing sensing possibilities. Turning again to FIG. 2, two [0117] sensing electrodes 26 and 28 are located on the electrically active surface 15 with electrical insulator rings 30 placed between the sense electrodes and the active surface. These canister sense electrodes could be switched off and electrically insulated during and shortly after defibrillation/cardioversion shock delivery. The canister sense electrodes may also be placed on the electrically inactive surface of the canister. In the embodiment of FIG. 2, there are actually four sensing electrodes, two on the subcutaneous lead and two on the canister. In the preferred embodiment, the ability to change which electrodes are used for sensing would be a programmable feature of the S-ICD to adapt to changes in the patient physiology and size (in the case of children) over time. The programming could be done via the use of physical switches on the canister, or as presently preferred, via the use of a programming wand or via a wireless connection to program the circuitry within the canister.
The canister could be employed as either a cathode or an anode of the S-ICD cardioversion/defibrillation system. If the canister is the cathode, then the subcutaneous coil electrode would be the anode. Likewise, if the canister is the anode, then the subcutaneous electrode would be the cathode. [0118]
The active canister housing will provide energy and voltage intermediate to that available with ICDs and most AEDs. The typical maximum voltage necessary for ICDs using most biphasic waveforms is approximately 750 Volts with an associated maximum energy of approximately 40 Joules. The typical maximum voltage necessary for AEDs is approximately 2000-5000 Volts with an associated maximum energy of approximately 200-360 Joules depending upon the model and waveform used. The S-ICD of the present invention uses maximum voltages in the range of about 700 to about 3150 Volts and is associated with energies of about 40 to about 210 Joules. The capacitance of the S-ICD could range from about 50 to about 200 micro farads. [0119]
The sense circuitry contained within the canister is highly sensitive and specific for the presence or absence of life threatening ventricular arrhythmias. Features of the detection algorithm are programmable and the algorithm is focused on the detection of V-FIB and high rate V-TACH (>240 bpm). Although the S-ICD of the present invention may rarely be used for an actual life threatening event, the simplicity of design and implementation allows it to be employed in large populations of patients at modest risk with modest cost by non-cardiac electrophysiologists. Consequently, the S-ICD of the present invention focuses mostly on the detection and therapy of the most malignant rhythm disorders. As part of the detection algorithm's applicability to children, the upper rate range is programmable upward for use in children, known to have rapid supraventricular tachycardias and more rapid ventricular fibrillation. Energy levels also are programmable downward in order to allow treatment of neonates and infants. [0120]
Turning now to FIG. 4, the optimal subcutaneous placement of the S-ICD of the present invention is illustrated. As would be evidence to a person skilled in the art, the actual location of the S-ICD is in a subcutaneous space that is developed during the implantation process. The heart is not exposed during this process and the heart is schematically illustrated in the figures only for help in understanding where the canister and coil electrode are three dimensionally located in the left mid-clavicular line approximately at the level of the inframammary crease at approximately the 5th rib. The [0121] lead 21 of the subcutaneous electrode traverses in a subcutaneous path around the thorax terminating with its distal electrode end at the posterior axillary line ideally just lateral to the left scapula. This way the canister and subcutaneous cardioversion/defibrillation electrode provide a reasonably good pathway for current delivery to the majority of the ventricular myocardium.
FIG. 5 illustrates a different placement of the present invention. The S-ICD canister with the active housing is located in the left posterior axillary line approximately lateral to the tip of the inferior portion of the scapula. This location is especially useful in children. The [0122] lead 21 of the subcutaneous electrode traverses in a subcutaneous path around the thorax terminating with its distal electrode end at the anterior precordial region, ideally in the inframammary crease. FIG. 6 illustrates the embodiment of FIG. 1 subcutaneously implanted in the thorax with the proximal sense electrodes 23 and 25 located at approximately the left axillary line with the cardioversion/defibrillation electrode just lateral to the tip of the inferior portion of the scapula.
FIG. 7 schematically illustrates the method for implanting the S-ICD of the present invention. An [0123] incision 31 is made in the left anterior axillary line approximately at the level of the cardiac apex. This incision location is distinct from that chosen for S-ICD placement and is selected specifically to allow both canister location more medially in the left inframammary crease and lead positioning more posteriorly via the introducer set (described below) around to the left posterior axillary line lateral to the left scapula. That said, the incision can be anywhere on the thorax deemed reasonably by the implanting physician although in the preferred embodiment, the S-ICD of the present invention will be applied in this region. A subcutaneous pathway 33 is then created medially to the inframmary crease for the canister and posteriorly to the left posterior axillary line lateral to the left scapula for the lead.
The S-[0124] ICD canister 11 is then placed subcutaneously at the location of the incision or medially at the subcutaneous region at the left inframmary crease. The subcutaneous electrode 13 is placed with a specially designed curved introducer set 40 (see FIG. 8). The introducer set comprises a curved trocar 42 and a stiff curved peel away sheath 44. The peel away sheath is curved to allow for placement around the rib cage of the patient in the subcutaneous space created by the trocar. The sheath has to be stiff enough to allow for the placement of the electrodes without the sheath collapsing or bending. Preferably the sheath is made out of a biocompatible plastic material and is perforated along its axial length to allow for it to split apart into two sections. The trocar has a proximal handle 41 and a curved shaft 43. The distal end 45 of the trocar is tapered to allow for dissection of a subcutaneous path 33 in the patient. Preferably, the trocar is cannulated having a central Lumen 46 and terminating in an opening 48 at the distal end. Local anesthetic such as lidocaine can be delivered, if necessary, through the lumen or through a curved and elongated needle designed to anesthetize the path to be used for trocar insertion should general anesthesia not be employed. The curved peel away sheath 44 has a proximal pull tab 49 for breaking the sheath into two halves along its axial shaft 47. The sheath is placed over a guidewire inserted through the trocar after the subcutaneous path has been created. The subcutaneous pathway is then developed until it terminates subcutaneously at a location that, if a straight line were drawn from the canister location to the path termination point the line would intersect a substantial portion of the left ventricular mass of the patient. The guidewire is then removed leaving the peel away sheath. The subcutaneous lead system is then inserted through the sheath until it is in the proper location. Once the subcutaneous lead system is in the proper location, the sheath is split in half using the pull tab 49 and removed. If more than one subcutaneous electrode is being used, a new curved peel away sheath can be used for each subcutaneous electrode.
The S-ICD will have prophylactic use in adults where chronic transvenous/epicardial ICD lead systems pose excessive risk or have already resulted in difficulty, such as sepsis or lead fractures. It is also contemplated that a major use of the S-ICD system of the present invention will be for prophylactic use in children who are at risk for having fatal arrhythmias, where chronic transvenous lead systems pose significant management problems. Additionally, with the use of standard transvenous ICDs in children, problems develop during patient growth in that the lead system does not accommodate the growth. FIG. 9 illustrates the placement of the S-ICD subcutaneous lead system such that he problem that growth presents to the lead system is overcome. The distal end of the subcutaneous electrode is placed in the same location as described above providing a good location for the coil cardioversion/[0125] defibrillation electrode 27 and the sensing electrodes 23 and 25. The insulated lead 21, however is no longer placed in a taught configuration. Instead, the lead is serpiginously placed with a specially designed introducer trocar and sheath such that it has numerous waves or bends. As the child grows, the waves or bends will straighten out lengthening the lead system while maintaining proper electrode placement. Although it is expected that fibrous scarring especially around the defibrillation coil will help anchor it into position to maintain its posterior position during growth, a lead system with a distal tine or screw electrode anchoring system 52 can also be incorporated into the distal tip of the lead to facilitate lead stability (see FIG. 1). Other anchoring systems can also be used such as hooks, sutures, or the like.
FIGS. 10 and 11 illustrate another embodiment of the present S-ICD invention. In this embodiment there are two [0126] subcutaneous electrodes 13 and 13′ of opposite polarity to the canister. The additional subcutaneous electrode 13′ is essentially identical to the previously described electrode. In this embodiment the cardioversion/defibrillation energy is delivered between the active surface of the canister and the two coil electrodes 27 and 27′. Additionally, provided in the canister is means for selecting the optimum sensing arrangement between the four sense electrodes 23, 23′, 25, and 25′. The two electrodes are subcutaneously placed on the same side of the heart. As illustrated in FIG. 6, one subcutaneous electrode 13 is placed inferiorly and the other electrode 13′ is placed superiorly. It is also contemplated with this dual subcutaneous electrode system that the canister and one subcutaneous electrode are the same polarity and the other subcutaneous electrode is the opposite polarity.
Turning now to FIGS. 12 and 13, further embodiments are illustrated where the [0127] canister 11 of the S-ICD of the present invention is shaped to be particularly useful in placing subcutaneously adjacent and parallel to a rib of a patient. The canister is long, thin, and curved to conform to the shape of the patient's rib. In the embodiment illustrated in FIG. 12, the canister has a diameter ranging from about 0.5 cm to about 2 cm without 1 cm being presently preferred. Alternatively, instead of having a circular cross sectional area, the canister could have a rectangular or square cross sectional area as illustrated in FIG. 13 without falling outside of the scope of the present invention. The length of the canister can vary depending on the size of the patient's thorax. Currently the canister is about 5 cm to about 15 cm long with about 10 being presently preferred. The canister is curved to conform to the curvature of the ribs of the thorax. The radius of the curvature will vary depending on the size of the patient, with smaller radiuses for smaller patients and larger radiuses for larger patients. The radius of the curvature can range from about 5 cm to about 35 cm depending on the size of the patient. Additionally, the radius of the curvature need not be uniform throughout the canister such that it can be shaped closer to the shape of the ribs. The canister has an active surface, 15 that is located on the interior (concave) portion of the curvature and an inactive surface 16 that is located on the exterior (convex) portion of the curvature. The leads of these embodiments, which are not illustrated except for the attachment port 19 and the proximal end of the lead 21, can be any of the leads previously described above, with the lead illustrated in FIG. 1 being presently preferred.
The circuitry of this canister is similar to the circuitry described above. Additionally, the canister can optionally have at least one sense electrode located on either the active surface of the inactive surface and the circuitry within the canister can be programmable as described above to allow for the selection of the best sense electrodes. It is presently preferred that the canister have two [0128] sense electrodes 26 and 28 located on the inactive surface of the canisters as illustrated, where the electrodes are spaced from about 1 to about 10 cm apart with a spacing of about 3 cm being presently preferred. However, the sense electrodes can be located on the active surface as described above.
It is envisioned that the embodiment of FIG. 12 will be subcutaneously implanted adjacent and parallel to the left anterior 5th rib, either between the 4th and 5th ribs or between the 5th and 6th ribs. However other locations can be used. [0129]
Another component of the S-ICD of the present invention is a cutaneous test electrode system designed to simulate the subcutaneous high voltage shock electrode system as well as the QRS cardiac rhythm detection system. This test electrode system is comprised of a cutaneous patch electrode of similar surface area and impedance to that of the S-ICD canister itself together with a cutaneous strip electrode comprising a defibrillation strip as well as two button electrodes for sensing of the QRS. Several cutaneous strip electrodes are available to allow for testing various bipole spacings to optimize signal detection comparable to the implantable system. [0130]
FIGS. [0131] 14 to 18 depict particular US-ICD embodiments of 11 the present invention. The various sensing, shocking and pacing circuitry, described in detail above with respect to the S-ICD embodiments, may additionally be incorporated into the following US-ICD embodiments. Furthermore, particular aspects of any individual S-ICD embodiment discussed above, may be incorporated, in whole or in part, into the US-ICD embodiments depicted in the following figures.
Turning now to FIG. 14, the US-ICD of the present invention is illustrated. The US-ICD consists of a curved housing [0132] 1211 with a first and second end. The first end 1413 is thicker than the second end 1215. This thicker area houses a battery supply, capacitor and operational circuitry for the US-ICD. The circuitry will be able to monitor cardiac rhythms for tachycardia and fibrillation, and if detected, will initiate charging the capacitor and then delivering cardioversion/defibrillation energy through the two cardioversion/ defibrillating electrodes 1417 and 1219 located on the outer surface of the two ends of the housing. The circuitry can provide cardioversion/defibrillation energy in different types of waveforms. In the preferred embodiment, a 100 uF biphasic waveform is used of approximately 10-20 ms total duration and with the initial phase containing approximately {fraction (2/3)} of the energy, however, any type of waveform can be utilized such as monophasic, biphasic, multiphasic or alternative waveforms as is known in the art.
The housing of the present invention can be made out of titanium alloy or other presently preferred ICD designs. It is contemplated that the housing is also made out of biocompatible plastic materials that electronically insulate the electrodes from each other. However, it is contemplated that a malleable canister that can conform to the curvature of the patient's chest will be preferred. In this way the patient can have a comfortable canister that conforms to the unique shape of the patient's rib cage. Examples of conforming ICD housings are provided in U.S. Pat. No. 5,645,586, the entire disclosure of which is herein incorporated by reference. In the preferred embodiment, the housing is curved in the shape of a 5th rib of a person. Because there are many different sizes of people, the housing will come in different incremental sizes to allow a good match between the size of the rib cage and the size of the US-ICD. The length of the US-ICD will range from about 15 to about 50 cm. Because of the primary preventative role of the therapy and the need to reach energies over 40 Joules, a feature of the preferred embodiment is that the charge time for the therapy, intentionally be relatively long to allow capacitor charging within the limitations of device size. [0133]
The thick end of the housing is currently needed to allow for the placement of the battery supply, operational circuitry, and capacitors. It is contemplated that the thick end will be about 0.5 cm to about 2 cm wide with about 1 cm being presently preferred. As microtechnology advances, the thickness of the housing will become smaller. [0134]
The two cardioversion/defibrillation electrodes on the housing are used for delivering the high voltage cardioversion/defibrillation energy across the heart. In the preferred embodiment, the cardioversion/defibrillation electrodes are coil electrodes, however, other cardioversion/defibrillation electrodes could be used such as having electrically isolated active surfaces or platinum alloy electrodes. The coil cardioversion/defibrillation electrodes are about 5-10 cm in length. Located on the housing between the two cardioversion/defibrillation electrodes are two [0135] sense electrodes 1425 and 1427. The sense electrodes are spaced far enough apart to be able to have good QRS detection. This spacing can range from 1 to 10 cm with 4 cm being presently preferred. The electrodes may or may not be circumferential with the preferred embodiment. Having the electrodes non-circumferential and positioned outward, toward the skin surface, is a means to minimize muscle artifact and enhance QRS signal quality. The sensing electrodes are electrically isolated from the cardioversion/defibrillation electrode via insulating areas 1423. Analogous types of cardioversion/defibrillation electrodes are currently commercially available in a transvenous configuration. For example, U.S. Pat. No. 5,534,022, the entire disclosure of which is herein incorporated by reference, discloses a composite electrode with a coil cardioversion/defibrillation electrode and sense electrodes. Modifications to this arrangement is contemplated within the scope of the invention. One such modification is to have the sense electrodes at the two ends of the housing and have the cardioversion/defibrillation electrodes located in between the sense electrodes. Another modification is to have three or more sense electrodes spaced throughout the housing and allow for the selection of the two best sensing electrodes. If three or more sensing electrodes are used, then the ability to change which electrodes are used for sensing would be a programmable feature of the US-ICD to adapt to changes in the patient physiology and size over time. The programming could be done via the use of physical switches on the canister, or as presently preferred, via the use of a programming wand or via a wireless connection to program the circuitry within the canister.
Turning now to FIG. 15, the optimal subcutaneous placement of the US-ICD of the present invention is illustrated. As would be evident to a person skilled in the art, the actual location of the US-ICD is in a subcutaneous space that is developed during the implantation process. The heart is not exposed during this process and the heart is schematically illustrated in the figures only for help in understanding where the device and its various electrodes are three dimensionally located in the thorax of the patient. The US-ICD is located between the left mid-clavicular line approximately at the level of the inframammary crease at approximately the 5[0136] ^thrib and the posterior axillary line, ideally just lateral to the left scapula. This way the US-ICD provides a reasonably good pathway for current delivery to the majority of the ventricular myocardium.
FIG. 16 schematically illustrates the method for implanting the US-ICD of the present invention. An [0137] incision 1631 is made in the left anterior axillary line approximately at the level of the cardiac apex. A subcutaneous pathway is then created that extends posteriorly to allow placement of the US-ICD. The incision can be anywhere on the thorax deemed reasonable by the implanting physician although in the preferred embodiment, the US-ICD of the present invention will be applied in this region. The subcutaneous pathway is created medially to the inframammary crease and extends posteriorly to the left posterior axillary line. The pathway is developed with a specially designed curved introducer 1742 (see FIG. 17). The trocar has a proximal handle 1641 and a curved shaft 1643. The distal end 1745 of the trocar is tapered to allow for dissection of a subcutaneous path in the patient. Preferably, the trocar is cannulated having a central lumen 1746 and terminating in an opening 1748 at the distal end. Local anesthetic such as lidocaine can be delivered, if necessary, through the lumen or through a curved and elongated needle designed to anesthetize the path to be used for trocar insertion should general anesthesia not be employed. Once the subcutaneous pathway is developed, the US-ICD is implanted in the subcutaneous space, the skin incision is closed using standard techniques.
As described previously, the US-ICDs of the present invention vary in length and curvature. The US-ICDs are provided in incremental sizes for subcutaneous implantation in different sized patients. Turning now to FIG. 18, a different embodiment is schematically illustrated in exploded view which provides different sized US-ICDs that are easier to manufacture. The different sized US-ICDs will all have the same sized and shaped [0138] thick end 1413. The thick end is hollow inside allowing for the insertion of a core operational member 1853. The core member comprises a housing 1857 which contains the battery supply, capacitor and operational circuitry for the US-ICD. The proximal end of the core member has a plurality of electronic plug connectors. Plug connectors 1861 and 1863 are electronically connected to the sense electrodes via pressure fit connectors (not illustrated) inside the thick end which are standard in the art. Plug connectors 1865 and 1867 are also electronically connected to the cardioverter/defibrillator electrodes via pressure fit connectors inside the thick end. The distal end of the core member comprises an end cap 1855, and a ribbed fitting 1859 which creates a water-tight seal when the core member is inserted into opening 1851 of the thick end of the US-ICD.
The core member of the different sized and shaped US-ICD will all be the same size and shape. That way, during an implantation procedures, multiple sized US-ICDs can be available for implantation, each one without a core member. Once the implantation procedure is being performed, then the correct sized US-ICD can be selected and the core member can be inserted into the US-ICD and then programmed as described above. Another advantage of this configuration is when the battery within the core member needs replacing it can be done without removing the entire US-ICD. [0139]
FIG. 14([0140] a) illustrates an embodiment of the subcutaneous 11 lead electrode or “lead electrode assembly” 100. The lead electrode assembly 100 is designed to provide an electrode 107 to be implanted subcutaneously in the posterior thorax of a patient for delivery of cardioversion/defibrillation energy. The lead electrode assembly 100 is further designed to provide a path for the cardioversion/defibrillation energy to reach the electrode 107 from the operational circuitry within the canister 11 of an S-ICD such as the embodiment shown in FIG. 1.
The [0141] lead electrode assembly 100 comprises a connector 111, a lead 21, a lead fastener 146, an electrode 107 and an appendage 118. The connector 111 is connected to the lead 21. The lead 21 is further connected to the electrode 107 with the lead fastener 146. The appendage 118 is mounted to the electrode 107.
The connector [0142] 111 provides an electrical connection between the lead 21 and the operational circuitry within the canister 11 of an S-ICD such as the embodiment shown in FIG. 1. Connector 111 is designed to mate with the connection port 19 on the canister 11. In the embodiment under discussion, the connector 111 meets the IS-1 standard.
The [0143] lead 21 of the lead electrode assembly 100 provides an electrical connection between the connector 111 and the electrode 107. The lead 21 comprises a distal end 101 and a proximal end 102. The distal end 101 of the lead 21 is attached to the connector 111. The proximal end 102 of the lead 21 is attached to electrode 107 with the lead fastener 146.
The [0144] lead 21 has a lead length, l_Lead, measured from the connector 111 along the lead 21 to the lead fastener 146 of the electrode 107. The length of the lead 21 is approximately 25 cm. In alternative embodiments, the lead lengths range between approximately 5 cm and approximately 52 cm.
The [0145] lead fastener 146 provides a robust physical and electrical connection between the lead 21 and the electrode 107. The lead fastener 146 joins the proximal end 102 of the lead 21 to electrode 107.
The [0146] electrode 107 comprises an electrically conductive member designed to make contact with the tissue of the patient and transfer cardioversion/defibrillation energy to the tissue of the patient from the S-ICD canister 11.
The [0147] electrode 107 illustrated is generally flat and planar, comprising a top surface 110, a bottom surface 115, a distal end 103 and a proximal end 104. The lead fastener 146 is attached to the top surface 110 of the distal end 103 of the electrode 107.
The [0148] electrode 107 may have shapes other than planar. In an alternate embodiment, the electrode 107 is shaped like a coil.
The [0149] appendage 118 is a member attached to the electrode 107 that can be gripped and used to precisely locate the lead electrode assembly 100 during its surgical implantation within the patient.
The [0150] appendage 118 has a first end 105, a second end 106, a distal edge 121 and a proximal edge 129. The second end 106 of the appendage 118 is attached to the top surface 110 of the electrode 107. The appendage 118 is positioned such that its proximal edge 129 is within approximately 20 mm of the proximal end 104 of the electrode 107. In alternate embodiments, the appendage 118 is attached to the electrode 107 in other positions.
It is useful at this point, to set out several general definitions for future reference in discussing the dimensions and placement of [0151] appendages 118.
The appendage height, h[0152] _Appendage, is defined as the distance from the point of the appendage 118 most distant from the electrode 107 to a point of the appendage 118 closest to the electrode 107 measured along a line perpendicular to the top surface 110 of the electrode 107. The appendage height of the appendage 118 illustrated, for example, would be measured between the first end 105 of the appendage 118 and the second end 106 of the appendage 118.
The appendage height of the [0153] appendage 118 illustrated is approximately 5 mm. In alternative embodiments, the appendage heights range between approximately 1 mm and approximately 10 mm.
The appendage interface is defined as the part of the [0154] appendage 118 that joins it to the electrode 107. The appendage interface of the appendage 118 illustrated, for example, would be the second end 106 of the appendage 118.
The appendage length, l[0155] _Appendage, is the length of the appendage 118 along the appendage interface. The appendage interface of the appendage 118 illustrated, for example, would be the length of the second end 106 of the appendage 118.
The appendage length of the [0156] appendage 118 illustrated in FIG. 14 is approximately 1 cm. In alternative embodiments, appendage lengths range between approximately 2 mm and approximately 6 cm. In an alternate embodiment, the appendage 118 is substantially as long as the electrode 107.
More particularly, the [0157] appendage 118 of the embodiment illustrated is a fin 120 comprising a fin core 122 (phantom view) and a coating 125.
The [0158] fin core 122 generally provides support for the fin 120. The fin core 122 has a first end 126 and a second end 127. The second end 127 of the fin core 122 is attached to the top surface 110 of the electrode 107.
The [0159] fin core 122 comprises a metal selected from the group consisting essentially of titanium, nickel alloys, stainless steel alloys, platinum, platinum iridium, and mixtures thereof. In other embodiments, the fin core 122 comprises any rugged material that can be attached to the first surface 110 of the electrode 107.
The [0160] coating 125 is disposed around the fin core 122. The coating 125 provides a surface for the fin 120 that can be easily gripped during the implantation of the lead electrode assembly 100. The coating 125 covering the fin core 122 is composed of molded silicone. In an alternative embodiment, the coating 125 may be any polymeric material. In this specification, the term polymeric material includes the group of materials consisting of a polyurethane, a polyamide, a polyeteretherketone (PEEK), a polyether block amide (PEBA), a polytetrafluoroethylene (PTFE), a silicone and mixtures thereof.
In one embodiment, the [0161] fin 120 is reinforced with a layer of Dacron® polymer mesh attached to the inside of the coating 125. Dacron® is a registered trademark of E.I. du Pont de Nemours and Company Corporation, Wilmington, Del. In another embodiment, the Dacron® polymer mesh attached to the outside of the coating 125. In another embodiment, the fin 120 is reinforced with a layer of any polymeric material. 5
FIG. 14([0162] b) illustrates a top view of the lead electrode assembly 100. The electrode 107 is substantially rectangular in shape, comprising a first pair of sides 108, a second pair of sides 109 and four corners 112. In an alternative embodiment the electrode 107 has a shape other than rectangular. In this embodiment, the corners 112 of the electrode 107 are rounded. In an alternative embodiment the corners 112 of the electrode 107 are not rounded.
The first pair of [0163] sides 108 of the electrode 107 are substantially linear, substantially parallel to each other and are approximately 1 cm in length. The second pair of sides 109 of the electrode 107 are also substantially linear, substantially parallel with each other and are approximately 5 cm in length. The bottom surface 115 of the electrode 107 has an area of approximately 500 square mm. In alternative embodiments, the first pair of sides 108 and the second pair of sides 109 of the electrode 107 are neither linear nor parallel.
In alternative embodiments, the length of the first pair of [0164] sides 108 and second pair of sides 109 of the electrode 107 range independently between approximately 1 cm and approximately 5 cm. The surface area of the bottom surface 115 of the electrode 107 ranges between approximately 100 sq. mm and approximately 2000 sq. mm. In one embodiment, the first pair of sides 108 and second pair of sides 109 of the electrode 107 are linear and of equal length, such that the electrode 107 is substantially square-shaped.
The [0165] electrode 107 comprises a sheet of metallic mesh 114 further comprised of woven wires 119. The metallic mesh 114 comprises a metal selected from the group consisting essentially of titanium, nickel alloys, stainless steel alloys, platinum, platinum iridium, and mixtures thereof. In other embodiments, the metallic mesh 114 comprises any conductive material.
In an alternate embodiment, the [0166] electrode 107 comprises a solid metallic plate. The metallic plate comprises a metal selected from the group consisting essentially of titanium, nickel alloys, stainless steel alloys, platinum, platinum iridium, and mixtures thereof. In other embodiments, the solid plate comprises any conductive material.
The [0167] metallic mesh 114 is approximately a 150 mesh, having approximately 150 individual wires 119 per inch. In alternative embodiments, the metallic mesh 114 ranges between approximately a 50 mesh and approximately a 200 mesh. In this embodiment, the diameter of the wires 119 of the mesh is approximately 1 mil. In alternative embodiments, the diameter of the wires 119 ranges between approximately 1 and approximately 5 mils.
The [0168] metallic mesh 114 is first prepared by spot welding together the wires 119 located along the first pair of sides 108 and second pair of sides 109 of the metallic mesh 114. The excess lengths of wires are then ground or machined flush, so as to produce a smooth edge and to form a smooth border 113. In an alternate embodiment, the wires 119 located along the first pair of sides 108 and second pair of sides 109 of the metallic mesh 114 are bent in toward the metallic mesh 114 to form a smooth border 113.
The [0169] fin 120 is attached to the top surface 110 of the electrode 107 in a position centered between the first pair of sides 108 of the electrode 107. In other embodiments, the fin 120 is not centered between the first pair of sides 108 of the electrode 107.
The [0170] fin 120 is planar shape comprising a first face 191 and a second face 192. The first face 191 and the second face 192 of the fin 120 are substantially parallel to the first pair of sides 108 of the electrode 107. In other embodiments, the first ace 191 and the second face 192 of the fin 120 are positioned in orientations other than parallel to the first pair of sides 108 of the electrode 107.
The [0171] first face 191 and the second face 192 of the fin 120 extend from and substantially perpendicular to the top surface 110 of the electrode 107. In an alternative embodiment, the first face 191 and the second face 192 of the fin 120 extend from the top surface 110 of the electrode 107 at other than right angles.
The [0172] fin core 122 of the fin 120 is spot welded to the metallic mesh 114 comprising the electrode 107. In another embodiment, the fin 120 may be composed entirely of a polymeric material and attached to the electrode 107 by means known in the art.
FIG. 14([0173] c) illustrates in detail a section of the lead 21 of this embodiment. The lead 21 comprises an electrically insulating sheath 141 and an electrical conductor 142.
The [0174] electrically insulating sheath 141 is disposed around the electrical conductor 142 (phantom view). The electrically insulating sheath 141 prevents the cardioversion/defibrillation energy passing through the electrical conductor 142 to the electrode from passing into objects surrounding the lead 21. The electrically insulating sheath 141, comprises a tube 149 disposed around the electrical conductor 142. The tube is composed of either silicone, polyurethane or composite materials. One skilled in the art will recognize that the tube 149 could alternately be composed of any insulating, flexible, bio-compatible material suitable to this purpose.
In this embodiment, the [0175] electrical conductor 142 comprises three highly-flexible, highly-conductive coiled fibers known as filars 147 (phantom view). These fibers are wound in a helical shape through the electrically insulating sheath 141. In an alternate embodiment, the filars lie as linear cables within the electrically insulating sheath 141. In another alternate embodiment, a combination of helically coiled and linear filars lie within the electrically insulating sheath 141.
FIG. 14([0176] d) illustrates a cross-section of a filar 147. The filars 147 of the embodiment illustrated comprise a metal core 144, a metal tube 143 and an insulating coating 140. The metal tube 143 is disposed around the metal core 144. The insulating coating 140 is disposed around the metal tube. The metal core 144 is made of silver and the metal tube 143 is made of MP35N® stainless steel, a product of SPS Technologies of Jenkintown, Pa. The insulating coating 140 is made of teflon. The filars 147 of this structure are available as DFT™ (drawn filled tube) conductor coil, available from Fort Wayne Metals Research Products Corp. of Fort Wayne, Ind.
In an alternative embodiment, the [0177] filars 147 further comprise an intermediate coating (not shown) disposed between the metal tube 143 and the insulating coating 140. This intermediate coating is made of platinum, iridium ruthenum, palladium or an alloy of these metals.
In another alternative embodiment, the [0178] filars 147 comprise DBS™ (drawn braised strands) also available from Fort Wayne Metals Research Products Corp. of Fort Wayne, Ind.
Turning now to FIG. 14([0179] e) a cross section of the lead fastener 146 is shown in detail. The lead fastener 146 provides a robust physical and electrical connection between the lead 21 and the electrode 107.
In this embodiment, the [0180] lead fastener 146 comprises a metal strip 157, a crimping tube 154 and a crimping pin 156. The metal strip 157 has a first end 150, a second end 151, and a middle portion 152. The first end 150 and second end 151 of the metal strip 157 are separated by the middle portion 152. The first end 150 and second end 151 of the metal strip 157 are attached to the electrode 107. In this embodiment, the first end 150 and second end 151 of the lead fastener 146 are spot welded to the top surface 110 of the metallic mesh 114 comprising the electrode 107. In other embodiments, other fastening methods known in the art can be used.
The [0181] middle portion 152 of the metal strip 157 is raised away from the electrode 107 to permit the crimping tube 154 and electrically insulating sheath 141 of the lead 21 to fit between the metal strip 157 and the electrode 107.
The [0182] middle portion 152 of the metal strip 157 contains a crimp point 148. The crimp point 148 squeezes the crimping tube 154 and electrically insulating sheath 141 of the lead 21 thereby gripping it, and thereby providing a robust structural connection between the lead 21 and the electrode 107.
The [0183] filars 147 of the lead 21 are situated between the crimping tube 154 and crimping pin 156. The crimping tube 154 has a crimping point 155 which causes the filars 147 to be squeezed between crimping tube 154 and crimping pin 156. A gap 159 in the electrically insulating sheath 141 allows the crimping tube 155 to make contact the electrode 107, thereby forming a robust electrical connection.
The [0184] metal strip 157, the crimping tube 154 and crimping pin IQ, 156 are each made of platinum iridium. In an alternative embodiment, the metal strip 157, crimping tube 154 and crimping pin 156 are each made of a metal selected from the group consisting essentially of titanium, nickel alloys, stainless steel alloys, platinum, platinum iridium, and mixtures thereof. In an alternative embodiment, the metal strip 157, crimping tube 154 and crimping pin 156 are each made of any conductive material.
FIG. 14([0185] f) illustrates an exploded view of the lead fastener 146. In other embodiments, other types of lead fasteners 146 known in the art are used.
FIG. 15([0186] a) illustrates an alternative embodiment of the lead electrode assembly 100. This embodiment is substantially similar to the lead electrode assembly 100 illustrated in FIGS. 14(a)-14(f). In this embodiment, however, the appendage 118 lacks a fin core 122. Moreover, as seen in FIG. 15(a) the lead electrode assembly 100 of this embodiment further comprises a backing layer 130 and stitching 139. The backing layer 130 acts to insulate the electrode 107 so that cardioversion/defibrillation energy may not pass to the tissue of the patient that surrounds the top surface 110 of the electrode 107. This has the effect of focusing the cardioversion/defibrillation energy toward the heart of the patient through the bottom surface 115 of the electrode 107.
The [0187] backing layer 130 comprises a base portion 158 and an integrated fin 120. The base portion 158 of the backing layer 130 comprises a first surface 131, a second surface 132, a first side 133 and a second side 134.
The [0188] base portion 158 of the backing layer 130 is attached to the electrode 107 such that the second surface 132 of the backing layer 130 lies directly adjacent to the top surface 110 of the electrode 107.
The [0189] base portion 158 of the backing layer 130 is formed so that the first side 133 and the second side 134 are substantially parallel and of substantially the same size as the first pair of sides 108 of the electrode 107.
FIG. 15([0190] b) illustrates a top view of the lead electrode assembly 100 of this embodiment. The base portion 158 of the backing layer 130 further comprises a distal end 137 and a proximal end 138.
The [0191] distal end 137 and proximal end 138 of the backing layer 130 are parallel to and of substantially the same size as the second pair of sides 109 (hidden) of the electrode 107. The backing layer 130 contains a notch 136 on its distal end 137, through which the lead fastener 146 rises.
The [0192] base portion 158 of the backing layer 130 is attached to the electrode 107 with stitching 139. The stitching is composed of nylon. In alternate embodiments, the stitching is composed of any polymeric material.
The [0193] backing layer 130 is composed of polyurethane. In an alternative embodiment, the backing layer is composed of molded silicone, nylon, or Dacron®. In alternative embodiments, the backing layer is composed of any polymeric material.
The [0194] integrated fin 120 of the backing layer 130 is formed from the same piece of material as the backing layer 130. The integrated fin 120 has the same shape and dimensions as the fin 120 of the embodiment in FIG. 14.
In one embodiment, the [0195] integrated fin 120 is reinforced with a layer of Dacron® polymer mesh attached to the integrated fin 120. In another embodiment, the integrated fin 120 is reinforced with a layer of any polymeric material.
FIG. 16([0196] a) illustrates an alternative embodiment of the lead electrode assembly 100. This embodiment is substantially similar to the lead electrode assembly 100 illustrated in FIGS. 14(a)-14(e). In this embodiment, however, the fin 120 has a different construction.
Here, [0197] fin 120 comprises a first fin section 165, a second fin section 160 and stitching 168. The first fin section 165 is a rectangular sheet of polymeric material comprising an inside face 167, an outside face 166, a first side 175 and a second side 174. The first side 175 and second side 174 of the first fin section 165 are substantially parallel and of substantially the same size.
A line [0198] 173 divides the first fin section 165 into a first half 171 and a second half 172. The line 173 runs parallel to the first side 175 of the first fin section 165. The first half 171 of the first fin section 165 lies on one side of line 173. The second half 172 of the first fin section 165 lies on the other side of the line 173.
The [0199] second fin section 160 is a rectangular sheet of polymeric material of the same size as the first fin section 165 comprising an inside face 162 and an outside face 161. The second fin section 160 is divided in half substantially similarly to the first fin section 165, thereby forming a first half 163 and a second half 164 of the second fin section 160.
In an alternate embodiment, the [0200] first fin section 165 and second fin section are not rectangular in shape. In an alternate embodiment, the first fin section 165 and second fin section have an oval shape.
The first half [0201] 171 of the first fin section 165 is fastened to the first half 163 of the second fin section 160. The inside face 167 of the first half 171 of the first fin section 165 faces the inside face 162 of the first half 163 of the second fin section 160. The first fin section 165 is fastened the second fin section 160 with stitching 168.
The [0202] fin 120 is attached to the top surface 110 of the electrode 107. To accomplish this, the second half 172 of the first fin section 165 is attached to the top surface 110 of the electrode 107 with the stitching 169. The second half 164 of the second fin section 160 is similarly attached to the top surface 110 of the electrode 107 with stitching (not shown).
In one embodiment, the [0203] fin 120 is reinforced with a layer of Dacron® polymer mesh positioned between the first fin section 165 and the second fin section 160 of the integrated fin 120. In another embodiment, the Dacron® polymer mesh is attached only to the first fin section 165 or the second fin section 160. In other embodiments, the integrated fin 120 is reinforced with a layer of any polymeric material attached to either or both fin sections.
The appendage height of the [0204] fin 120 in this embodiment is approximately 5 mm. In alternative embodiments, the appendage heights range between approximately 1 mm and approximately 10 mm. The appendage length of the fin 120 in this embodiment is approximately 1 cm. In alternative embodiments, appendage lengths range between approximately 2 mm and approximately 6 cm. In one embodiment, the appendage length of the fin 120 is such that the fin 120 is substantially as long as the electrode 107.
FIG. 17([0205] a) illustrates a side plan view of an alternative embodiment of the lead electrode assembly 100. The lead electrode assembly 100 comprises a connector 111, a lead 21, a lead fastener 146, an electrode 107, a backing layer 130 with an integrated fin tab 180, a molded cover 220 and an appendage 118.
The connector [0206] 111 is connected to the lead 21. The lead 21 is further connected to the electrode 107 with the lead fastener 146. The backing layer 130 is positioned over the electrode 107. The fin tab 180 protrudes from the backing layer 130. The molded cover 220 is disposed around the lead fastener 146 and the backing layer 130. The molded cover 220 is further disposed around the fin tab 180 of the backing layer 118 to form the appendage 118. The molded cover 220 also partially envelops the electrode 107.
The connector [0207] 111 and the lead 21 are substantially similar to the connector 111 and the lead 21 described with reference to FIGS. 14(a)-14(f). The lead comprises a distal end 101 and a proximal end 102. The distal end 101 of the lead 21 is attached to the connector 111. The proximal end 102 of the lead 21 is connected to the electrode 107 by the lead fastener 146.
In this embodiment, the [0208] lead fastener 146 comprises a first crimping tube 200, a crimping pin 202 and a second crimping tube 201. The first crimping tube 200 connects the proximal end 102 of the lead 21 to the crimping pin 202. The second crimping tube 201 connects the crimping pin 202 to the electrode 107.
The [0209] electrode 107 comprises a distal end 103 (phantom view), a proximal end 104, a top surface 110 and a bottom surface 115. The electrode further comprises three sections: a main body 217, a mandrel 219 and a mandrel neck 218.
The [0210] main body 217 of the electrode 107 is the region of the electrode 107 that makes contact with the tissue of the patient and transfers the cardioversion/defibrillation energy to the patient. This region is substantially rectangular, comprising a first pair of sides 108 (not shown) and a second pair of sides 109. The first pair of sides 108 of the electrode 107 are substantially parallel to each other. The second pair of sides 109 of the electrode 107 are also substantially parallel to each other. In another embodiment, the first pair of sides 108 and the second pair of sides 109 of the electrode 107 are nonparallel. The main body 217 of the electrode 107 is positioned under the backing layer 130, so that the top surface 110 of the electrode faces the backing layer 130.
The [0211] mandrel 219 is a region of the electrode 107 shaped to facilitate the connection of the electrode 107 to the lead 21 via the lead fastener 146. The mandrel of the electrode is crimped onto to the crimping pin 202 of the lead fastener 146 with the second crimping tube 201, SO that a robust physical and electrical connection is formed. The main body 217 of the electrode 107 is connected to the mandrel 219 of the electrode 107 via the mandrel neck 218 of the electrode 107.
The [0212] backing layer 130 comprises a base portion 158 and an integrated fin tab 180. The base portion 158 of the backing layer 130 comprises a first surface 131, a second surface 132, a distal end 137 and a proximal end 138.
The [0213] base portion 158 of the backing layer 130 is positioned such that its second surface 132 is adjacent to the top surface 110 of the electrode 107. The base portion 158 of the backing layer 130 is sized and positioned so that the distal end 137 and proximal end 138 of the base portion 158 of the backing layer 130 overlay the second pair of sides 109 of the main body 217 of the electrode 107. The distal end 137 and proximal end 138 of the are also substantially parallel and of substantially the same size as the second pair of sides 109 of the electrode 107.
The integrated [0214] fin tab 180 of the backing layer 130 is formed from the same piece of material as the base portion 158 of the backing layer 130. The integrated fin tab 180 is formed on the first surface 131 of the base portion 158 of the backing layer 130.
The integrated [0215] fin tab 180 comprises a proximal edge 183, a distal edge 184, a top 185 and a bottom 186. The bottom 186 of the integrated fin tab 180 is joined to the first surface 131 of the base portion 158 of the backing layer 130. The proximal edge 183 and the distal edge 184 of the integrated fin tab 180 extend from, and substantially perpendicular to the first surface 131 of the base portion 158 of the backing layer 130. The proximal edge 183 and distal edge 184 of the integrated fin tab 180 are parallel with each other. The integrated fin tab 180 is positioned so that its proximal edge 183 is substantially flush with the proximal end 138 of the base portion 158 of the backing layer 130.
The [0216] backing layer 130 is composed of polyurethane. In an alternative embodiment, the backing layer 130 is composed of silicone. In another alternative embodiment, the backing layer 130 is composed of any polymeric material.
The molded [0217] cover 220 envelops and holds together the components of the lead electrode assembly 100. The molded cover 220 also provides rigidity to the lead electrode assembly 100. The molded cover 220 envelops the lead fastener 146 and the backing layer 130. The fin 120 is formed when the molded cover 220 covers the fin tab 180. The thickness of the resulting fin 120 is approximately 2 mm. In alternate embodiments, the thickness of the fin 120 is between approximately 1 mm and approximately 3 mm.
The appendage height of the [0218] fin 120 in this embodiment is approximately 5 mm. In alternative embodiments, the appendage heights range between approximately 1 mm and approximately 10 mm. The appendage length of the fin 120 in this embodiment is approximately 1 cm. In alternative embodiments, appendage lengths range between approximately 2 mm and approximately 6 cm. In one embodiment, the appendage length of the fin 120 is such that the fin is as long as the backing layer. In one embodiment, the appendage length of the fin 120 is such that the fin is as long as the electrode 107. In one embodiment, the appendage length of the fin 120 is such that the fin is as long as the molded cover 220.
The molded [0219] cover 220 also partially covers the bottom surface 115 of the electrode 107. In this way, the molded cover 220 attaches the backing layer 130 to the electrode 107.
The molded [0220] cover 220 in this embodiment is made of silicone. In an alternate embodiment, the molded cover 220 is made of any polymeric material. Stitching 360 holds the molded cover 220, the electrode 107 and the backing layer 130 together.
In one embodiment, the [0221] fin 120 is reinforced with a layer of Dacron® polymer mesh positioned between the molded cover 220 and the integrated fin tab 180. In another embodiment, the Dacron® polymer mesh is attached only to the molded cover 220. In other embodiments, the fin 120 is similarly reinforced with a layer of any polymeric material.
As shown in FIG. 17([0222] b), the fin 120 of the embodiment illustrated in FIG. 17(a) can alternately have a sloped shape. The sloped shape can reduce the resistance offered by the tissue of the patient as it slides against the fin 120 during the insertion of the lead electrode assembly 100 into the patient. The slope-shaped fin 120 is constructed so that the proximal edge 183 and distal edge 184 of the integrated fin tab 180 are not parallel with each other. Instead, proximal edge 183 of the integrated fin tab 180 can be curved so that the proximal edge 183 of the integrated fin tab 180 is closer to the proximal edge 184 at the top 185 of the integrated fin tab 180, than at the bottom 186 of the integrated fin tab 180. In alternate embodiments, the proximal edge 183 of the integrated fin tab 180 is not curved. Instead, the proximal edge 183 of the integrated fin tab 180 is straight, and forms an acute angle with the first surface 131 of the backing layer 130. In one alternate embodiment, the proximal edge 183 of the integrated fin tab 180 forms a 45 degree angle with the first surface 131 of the backing layer 130. In alternate embodiments, the distal edge 184 of the integrated fin tab 180 is curved. In alternate embodiments, the distal edge 184 of the integrated fin tab 180 is straight and shaped so that it forms an acute angle with the first surface 131 of the backing layer 130.
FIG. 17([0223] c) illustrates a front plan view of the lead electrode assembly 100 seen in FIG. 17(a). The base portion 158 of the backing layer 130 further comprises a first side 133 and second side 134. The first side 133 and second side 134 of the base portion 158 of the backing layer 130 are substantially parallel. In an alternate embodiment, the first side 133 and second side 134 of the backing layer 130 are not parallel. The base portion 158 of the backing layer 130 is sized so that it is substantially the same size and shape as the main body 217 of the electrode 107.
The integrated [0224] fin tab 180 of the backing layer 130 is planar, comprising a first face 181 and a second face 182. The first face 181 and second face 182 of the fin tab 180 are substantially parallel with each other and with the first side 133 and second side 134 of the backing layer 130. The first face 181 and second face 182 of the fin tab 180 extend from, and substantially perpendicular to the first surface 131 of the backing layer 130. In another embodiment, the first face 181 and second face 182 of the fin tab 180 extend from the first surface 131 of the backing layer 130 at angles other than a right angle.
In an alternate embodiment, the [0225] first face 181 and a second face 182 of the integrated fin tab 180 of the backing layer 130 are not substantially parallel to each other. Instead, they are angled, such that they are closer together at the top 185 than they are at the bottom 186 of the integrated fin tab 180. This shape can reduce the resistance offered by the tissue of the patient as it slides against the fin 120 during the insertion of the lead electrode assembly 100 into the patient.
In another embodiment, the [0226] first face 181 and a second face 182 of the integrated fin tab 180 of the backing layer 130 are angled, such that they are further apart at the top 185 than they are at the bottom 186 of the integrated fin tab 180. This shape can make the fin 120 easier to grip with a tool, such as a hemostat.
The [0227] fin tab 180 extends from the backing layer 130 at a position centered between the first side 133 and the second side 134 of the backing layer 130. In an alternate embodiment, the fin tab 180 is not centered between the first side 133 and the second side 134 of the backing layer 130.
An [0228] eyelet 301 is formed in the fin 120 of this embodiment. The eyelet can be used to facilitate the capture of the lead electrode assembly by a tool. The eyelet is formed as a hole 225 through the molded cover 220 and between the faces 181 and 182 of fin tab 180. In an alternate embodiment, no eyelet is formed in the fin 120.
The [0229] bottom surface 115 of the electrode 107 comprises a periphery 213 and a center 211. The molded cover 220 forms a skirt 222 around the periphery 213 of the bottom surface 115 of the electrode 107. The skirt 222 of the molded cover 220 covers the periphery 213 of the bottom surface 115 of the electrode 107.
The [0230] skirt 222 of the molded cover 220 can act to focus cardioversion/defibrillation energy emitted from the electrode 107 of the lead electrode assembly 100 toward the heart of the patient. Because the thorax of a patient is surrounded by a layer of fat that is somewhat conductive, the cardioversion/defibrillation energy may tend to arc through this layer to reach the active surface 15 of the canister 11 (seen in FIG. 1) without passing through the patient's heart. The skirt 222 of the lead electrode assembly 100 acts to minimize the loss of cardioversion/defibrillation energy to surrounding body tissues, or from being diverted away from the patient's heart.
The [0231] center 211 of the bottom surface 115 of the electrode 107 is not covered by the molded cover 220 and is left exposed. The width of the periphery 213 of the bottom surface 115 of the electrode 107 covered by the molded cover 220 is approximately 0.125 cm.
The area of the exposed [0232] center 211 of the bottom surface 115 of the electrode 107 is approximately 500 square mm. In alternative embodiments, the length of the first pair of sides 108 and the second pair of sides 109 of the electrode 107 vary, such that the area of the center 211 of the bottom surface 115 of the electrode has a surface area between approximately 100sq. mm. and approximately 2000 sq. mm.
FIG. 17([0233] d) illustrates an exploded top view of the lead fastener 146 of the embodiments illustrated in FIGS. 17(a)-17(c). The lead fastener connects the proximal end 102 of the lead 21 and the distal end 103 of the electrode 107.
In this embodiment, the [0234] lead fastener 146 comprises a first crimping tube 200, a crimping pin 202 and a second crimping tube 201. The crimping pin 202 comprises a first side 203 and a second side 204.
The crimping [0235] tube 200 crimps the filars 147 of the lead 21 (here, only one representative filar 147 is shown) to the first side 203 of crimping pin 202. The mandrel 219 of the electrode 107 is then wrapped around the second side 204 of the crimping pin 202. Crimping tube 201 crimps the mandrel 219 to the second side 204 of the crimping pin 202.
The first crimping [0236] tube 200, the second crimping tube 201 and the crimping pin 202 are each made of platinum iridium. In an alternative embodiment, the first crimping tube 200, the second crimping tube 201 and the crimping pin 202 are each made of a metal selected from the group consisting essentially of titanium, nickel alloys, stainless steel alloys, platinum, platinum iridium, and mixtures thereof. In other embodiments, the first crimping tube 200, the second crimping tube 201 and the crimping pin 202 each comprise any conductive material.
The [0237] electrode 107 in this embodiment comprises a sheet of metallic mesh 206 prepared by the process described with reference to FIG. 14. The electrode 107 has a width measured parallel to the second pair of sides 109 of the electrode 107. The width of the mandrel neck 218 of the electrode 107 is approximately 3 mm wide. The width of the mandrel of the electrode 107 is approximately 5 mm wide.
The first pair of [0238] sides 108 of the electrode 107 are approximately 5 cm in length. The second pair of sides 109 of the electrode 107 are approximately 1.9 cm in length. In alternative embodiments, the length of the first pair of sides 108 and the second pair of sides 109 of the electrode 107 range independently from approximately 1 cm to approximately 5 cm.
The [0239] electrode 107 of this embodiment further comprises four corners 112. The corners 112 of the electrode 107 are rounded. In an alternate embodiment, the corners 112 of the electrode 107 are not rounded.
FIGS. [0240] 17(e)-17(g) illustrate the size and position of the fin 120 on the molded cover of the lead electrode assembly 100.
FIGS. [0241] 18(a)-18(c) illustrate an alternative embodiment of the lead electrode assembly 100. This embodiment is substantially similar to the embodiments illustrated in FIGS. 17(a)-17(g). In this embodiment, however, the appendage height of the fin 120 is approximately 1 cm. The appendage length of the fin 120 in this embodiment is approximately 3.5 cm.
As shown in FIG. 18([0242] a), stitching 302 is placed through the molded cover 220 and the fin 120 to prevent the molded cover 220 from sliding off the fin tab 180 when the molded cover 220 is subjected to a force directed away from the electrode 107.
As shown in FIG. 18([0243] c), the fin 120 (phantom view) extends approximately two thirds of the length of the electrode 107.
FIG. 19 illustrates an alternative embodiment of the [0244] lead electrode assembly 100. This embodiment is substantially similar to the embodiments illustrated in FIGS. 17(a)-17(g). In this embodiment, however, the backing layer 130 (not shown) inside the molded cover 220 is curved. This results in an electrode 107 that has a curvature of radius r, such that the bottom surface 115 of the electrode 107 is concave.
Because a [0245] curved electrode 107 may more closely approximate the curvature of the patient's ribs, this curvature may have the effect of making the lead electrode assembly 100 more comfortable for the patient. In one embodiment, the radius r of the curvature varies throughout the electrode 107 such that it is intentionally shaped to approximate the shape of the ribs. Lead electrode assemblies 100 can be custom manufactured with an electrode 107 with a curvature r that matches the curvature of the intended patient's ribcage in the vicinity of the ribcage adjacent to which the electrode 107 is to be positioned.
In an alternative embodiment, [0246] lead electrode assemblies 100 are manufactured with an electrode 107 with a radius r that matches the curvature of the ribcage of a statistically significant number of people.
In another embodiment, [0247] lead electrode assemblies 100 with electrodes 107 of varying curvatures can be manufactured to allow an electrode radius r to be selected for implantation based on the size of the patient. Smaller radii can be used for children and for smaller adult patients. Larger radii can be used for larger patients. The radius r of the curvature can range from approximately 5 cm to approximately 35 cm depending on the size of the patient.
In an alternative embodiment, the [0248] electrode 107 of the lead electrode assembly 100 is flexible, such that it can be bent to conform to the curvature of the intended patient's rib cage at the time of implantation.
FIGS. [0249] 20(a)-20(c) illustrate an alternative embodiment of the lead electrode assembly 100. This embodiment is substantially similar to the embodiments illustrated in FIGS. 17(a)-17(g). In this embodiment, however, the backing layer 130 lacks an integrated fin tab 180 mounted on the first surface 131 of the backing layer 130. Moreover, this embodiment further comprises a backing layer 400 having a fin tab 405.
FIGS. [0250] 20(a) and 20(b) illustrate only the backing layer 400, the fin tab 405 and the electrode 107 of this embodiment as they are positioned relative to each other in the complete embodiment. Other components of the embodiment are not shown. FIG. 20(c) shows the embodiment in a complete form.
FIG. 20([0251] a) illustrates a top plan view of the backing layer 400 and the electrode 107. The backing layer 400 is positioned over the electrode 107. The electrode 107 of this embodiment is substantially similar to the electrode 107 of the embodiment illustrated in FIG. 17(d). In the complete embodiment, the mandrel 219 of the electrode 107 is joined to the lead 21 (not shown) by a lead fastener 146 (not shown) as shown in FIG. 17(a).
The [0252] backing layer 400 is a flat, planar member comprising a distal end 137 and a proximal end 138. The backing layer 400 further comprises a first side 133, a second side 134, a first surface 131, and a second surface 132 (not shown). The backing layer 400 further comprises a width, W, measured as the distance between the first side 133 and the second side 134.
The [0253] backing layer 400 includes a fin tab 405 that is formed from the same piece of material as the backing layer 400. The first side 133 of the backing layer 400 lies over one of the first pair of sides 108 of the electrode 107 except over a fin tab region 407. In the fin tab region 407, the backing layer 400 is wider than the electrode 107. In the fin tab region 407, the first side 133 forms a fin tab 405 that protrudes from part of the first side 133 of the backing layer 400 outside the fin tab region 407. The fin tab 405 extends from the first side 133 of the backing layer 400 in an orientation substantially parallel to the top surface 110 of the electrode 107, beyond the first side 108 (phantom view) of the electrode 107.
The [0254] fin tab 405 comprises a first face 410 and a second face 411 (not shown). The first face 410 of the fin tab 405 is an extension of the first surface 131 of the backing layer 400. The second face 411 of the fin tab 405 is an extension of the second surface 132 of the backing layer 400.
Aside from the [0255] fin tab 405, the backing layer 405 is formed so that it is of substantially the same size and shape as the main body 217 of the electrode 107.
The [0256] backing layer 400, including the fin tab 405, is composed of polyurethane. In an alternate embodiments the backing layer 400 and fin tab 405 are composed of any polymeric material.
FIG. 20([0257] b) is a side plan view of the backing layer 400 and the electrode 107. The backing layer 400 is positioned over the electrode 107 such that the second surface 132 of the backing layer 400 is placed adjacent to the top surface 110 of the electrode 107.
FIG. 20([0258] c) illustrates a bottom plan view of the complete embodiment, in which the backing layer 400 (not shown), the lead fastener 146 (not shown) and the fin tab 405 (phantom view) are coated with a molded cover 220. When the molded cover 220 is applied over the backing layer 400, a fin 424 is formed over the fin tab 405 (phantom view). The fin 424 comprises a proximal end 404 and a distal end 403.
In one embodiment, the [0259] fin 424 is reinforced with a layer of Dacron® polymer mesh positioned between the molded cover 220 and the fin tab 405. In another embodiment, the Dacron® polymer mesh is attached only to the molded cover 220. In other embodiments, the fin 424 is similarly reinforced with a layer of any polymeric material.
The appendage height, h[0260] _Appendage, of the fin 424 of this embodiment is approximately 5 mm. In alternative embodiments, the appendage heights range between approximately 1 mm and approximately 10 mm. The appendage length, L_Appendage, of the fin 424 of this embodiment is measured between the proximal end 404 and the distal end 403 of the fin 424. L_Appendageis measured where the fin 424 joins the rest of the lead electrode assembly 100. In this embodiment, the appendage length is approximately 1 cm. In alternative embodiments, the appendage lengths range between approximately 2 mm and approximately 6 cm. In one embodiment, the appendage length of the fin 424 is such that the fin 424 runs the length of the electrode 107. In one embodiment, the appendage length of the fin 424 is such that the fin 424 runs the length of the backing layer 130 (not shown). In one embodiment, the appendage length of the fin 424 is such that the fin 424 runs the length of the molded cover 220.
FIG. 20([0261] d) illustrates a bottom plan view of an alternate embodiment of the lead electrode assembly 100. This embodiment is substantially similar to the lead electrode assembly 100 illustrated in FIGS. 20(a)-20(c). In this embodiment, however, proximal end 404 of the fin 424 is sloped. The slope shape of the fin 424 is formed by the shape of the fin tab 405 (phantom view) inside the fin 424. The backing layer 400 gradually widens in the fin tab region 407 (not shown) with distance from the proximal end 138 (not shown) to the distal end 137 (not shown) of the backing layer 130 (not shown) until the appendage height is reached. The proximal end 404 of the fin 424 is straight and forms an acute angle with the first side 133 of the base portion 158 of the backing layer 130 (not shown). In an alternate embodiment, the proximal end 404 of the fin 424 forms a 45 degree angle with the first side 133 of the base portion 158 of the backing layer 130 (not shown). In another embodiment, the proximal end 404 of the fin 424 is curved slope.
In alternate embodiments, the [0262] distal end 403 of the fin 424 is straight and shaped so that it forms an acute angle with the first side 133 of the base portion 158 of the backing layer 130 (not shown). In alternate embodiments, the distal end 403 of the fin 424 is curved.
FIGS. [0263] 21(a)-21(c) illustrate an alternative embodiment of the lead electrode assembly 100. This embodiment is substantially similar to the embodiment illustrated in FIGS. 15(a)-15(b). The integrated fin 120 is absent, however, from the backing layer 130.
The [0264] lead electrode assembly 100 of this embodiment further comprises a cylindrical rod 500 having a loop 515 formed therein. The loop 515 comprises the appendage 118 of this embodiment. The loop 515 is a member attached to the electrode 107 that can be gripped and used to precisely locate the electrode 107 during its surgical implantation within the patient.
FIG. 21([0265] a) illustrates a side plan view of the embodiment. The cylindrical rod 500 comprises a first straight portion 510, a second straight portion 512 and a portion formed into a loop 515. The first straight portion 510 is separated from the second straight portion 512 by the loop 515.
The [0266] rod 500 is made of platinum iridium. In an alternative embodiment, the rod 500 is made of titanium or platinum.
The first [0267] straight portion 510 and second straight portion 512 are spot welded to the top surface 110 of the electrode 107. The loop 515 in the rod 500 extends away from the top surface 110 of the electrode 107.
The [0268] backing layer 130 is similar to the backing layer 130 illustrated in FIGS. 15(a)-15(b). The backing layer 130 is disposed over the electrode 107. The first straight portion 510 and second straight portion 512 of the rod 500 are positioned between the second surface 132 of the backing layer 130 and the top surface 110 of the electrode 107.
FIG. 21([0269] b) illustrates a cross-sectional rear plan view of the embodiment of the lead electrode assembly shown in FIG. 21(a). The first straight portion 510 and second straight portion 512 are positioned such that they are parallel to the first pair of sides 108 of the electrode 107. The first straight portion 510 and second straight portion 512 are both centered between the first pair of sides 108 of the electrode 107. In an alternative embodiment, the first straight portion 510 and second straight portion 512 are not parallel to and centered between the first pair of sides 108 of the electrode 107.
FIG. 21([0270] c) illustrates a top plan view of the embodiment of the lead electrode assembly shown in FIG. 21(a). An aperture 517 is formed in the backing layer 130. The aperture 517 in the backing layer is positioned such that the loop 515 extends through and beyond the aperture 517 in a direction away from the top surface 110 of the electrode 107. The backing layer 130 is attached to the electrode 107 with stitching 139.
FIGS. [0271] 22(a)-22(d) illustrate an alternative embodiment of the lead electrode assembly 100. This embodiment is substantially similar to the embodiment illustrated in FIGS. 15(a)-15(b). This embodiment comprises a backing layer 610, however, that lacks the integrated fin 120 illustrated in FIGS. 15(a)-15(b).
FIG. 22([0272] a) illustrates a top plan view of the backing layer 610 of this embodiment prior to its attachment to the rest of the lead electrode assembly 100. The backing layer 610 is cut in a pattern as shown. The backing layer comprises a first surface 131, a second surface 132 (not shown), a distal end 137, a proximal end 138, a first side 133, a second side 134 and an indented fin-forming region 620. The indented fin-forming region 620 comprises a first edge 690 and a second edge 691.
The [0273] backing layer 610 is formed so that the first side 133 and the second side 134 are substantially parallel and of substantially the same size as the first pair of sides 108 of the electrode 107. The proximal end 138 is formed so that it is substantially perpendicular to the first side 133 and the second side 134 of the backing layer 610. The proximal end 138 is longer than the second pair of sides 109 of the electrode 107 by a length A. The backing layer 610 has a varying width C measured from its distal end 137 to its proximal end 138 along a line parallel to its first side 133.
The backing layer is divided into three sections. A [0274] first backing section 693, a second backing section 692 and an ID indented fin-forming region 620 of length A. The length of the fin-forming region 620, A, is approximately 10 mm. In other embodiments, the length of the fin-forming region 620, A, ranges between approximately 2 mm and approximately 20 mm.
The area within the indented fin-forming [0275] region 620 is equally divided into a first fin area 612 and a second fin area 615. The dividing line 617 between the first fin area 612 and the second fin area 615 is substantially parallel to the first side 133.
The width, C, of the [0276] backing layer 610 is equal to the distance between the second pair of sides 109 of the electrode 107 except in the indented fin-forming region 620. In the indented fin-forming region 620, the width, C, of the backing layer 610 is B. The width, B, of the backing layer 610 in the fin-forming region 620, is approximately 1 cm. In alternate embodiments, the width, B, of the backing layer 610 in the fin-forming region 620 ranges between approximately 2 mm and approximately 6 cm. In other embodiments, however, the fin-forming region 620 ranges between 2 mm and the width, C, of the backing layer 610. In other embodiments, the fin-forming region 620 is longer than the width, C, of the backing layer 610.
The variation in width between the areas inside and outside the indented fin-forming [0277] region 620, forms the first edge 690 and a second edge 691 of the fin-forming region 620.
A first notch [0278] 136(a) is formed on the distal end 137 the first edge 690 of the fin-forming region 620 of the backing layer 130. A second notch 136(b) is formed on the distal end 137 the second edge 691 of the fin-forming region 620 of the backing layer 130.
The [0279] backing layer 610 in this embodiment is formed of flexible silicone. In alternative embodiments the backing layer 610 is formed of any bio-compatible, flexible polymeric material.
FIG. 22([0280] b) illustrates a top plan view of the lead electrode assembly 100 of this embodiment. The backing layer 610 is attached to the electrode 107, so that the first edge 690 and a second edge 691 of the fin-forming region 620 of the backing layer 610 meet. This causes the backing layer 610 in the first fin area 612 and the second fin area 615 to fold together to form a fin 120.
The first notch [0281] 136(a) and second notch 136(b) formed on the distal end 137 the first edge 690 and second edge 691 of the fin-forming region 620 of the backing layer 130 meet to form a notch 136 on the distal end 137 of the backing layer, through which the lead fastener 146 rises. Stitching 660 holds the backing layer to the electrode 107.
FIG. 22([0282] c) illustrates a side plan view of the lead electrode assembly 100 of this embodiment. Stitching 660 holds the first fin area 612 and a second fin area 615 of the backing layer 610 together to form the fin 120.
FIG. 22([0283] d) illustrates a front plan view of the lead electrode assembly 100 of this embodiment. In one embodiment, the fin 120 is reinforced with a layer of Dacron® polymer mesh positioned between the first fin area 612 and a second fin area 615. In another embodiment, the Dacron® polymer mesh is attached only to either first fin area 612 or the second fin area 615. In other embodiments, the fin 120 is similarly reinforced with a layer of any polymeric material.
FIGS. [0284] 22(e) and 22(f) illustrate an alternative embodiment of the lead electrode assembly 100. This embodiment is substantially similar to the embodiment illustrated in FIGS. 22(a)-22(d). The backing layer 610 is substantially similar to the backing layer 610 illustrated in FIG. 22(a). The backing layer 610 in this embodiment, however, is cut along line 617. The fin 120 of this embodiment comprises a proximal edge 129. The proximal edge 129 of the fin 120 is slope-shaped. The sloped shape can reduce the resistance offered by the tissue of the patient as it slides against the fin 120 during the insertion of the lead electrode assembly 100 into the patient.
FIGS. [0285] 23(a) and 23(b) illustrate a property of the embodiment of the lead electrode assembly 100 illustrated in FIGS. 22(e) and 22(f). The backing layer 610 is flexible, such that the substantially planar fin 120 formed therefrom is flexible and able to fold. Because the ability of the fin 120 to fold effectively reduces its appendage height, it may make the fin more comfortable to the patient after it is implanted.
FIG. 23([0286] a) shows fin 120 in an upright condition. When pressure is applied perpendicular to the first surface 131 of backing layer in the first fin area 612, along line 677 for example, the fin 120 folds as shown in FIG. 23(b). When the fin 120 folds, its appendage height, H_Appendage, is reduced. This can be seen by a comparison between FIG. 23(a) and FIG. 23(b).
The [0287] backing layer 610 in this embodiment is formed of a polymeric material. In an alternative embodiment, the backing layer 610 is formed of any bio-compatible, flexible polymeric material.
FIGS. [0288] 24(a)-24(c) illustrate an alternative embodiment of the lead electrode assembly 100. This embodiment is substantially similar to the embodiment illustrated in FIGS. 22(a)-22(d).
As shown in FIG. 24([0289] a), however, the material from the first fin area 612 and the second fin area 615 of the backing layer 610 is not fastened together with stitching 660 in this embodiment. The resulting appendage 118 is formed in the shape of a tube.
In alternate embodiments, the [0290] backing layer 610 is coupled to the electrode 107 such that the material from the first fin area 612 and the second fin area 615 of the backing layer 610 does not touch except at the dividing line 617 between the first fin area 612 and the second fin area 615. The separation between the first fin area 612 and the second fin area 615 of the backing layer 610 can allow the appendage 118 of this embodiment to be highly flexible. This flexibility can reduce the resistance offered by the tissue of the patient as it slides against the appendage 118 during the insertion of the lead electrode assembly 100 into the patient.
FIG. 24([0291] b) illustrates a side plan view of the embodiment illustrated in FIG. 24(a). The appendage 118 of this embodiment comprises a proximal edge 129. The proximal edge 129 of the appendage 118 is slope-shaped. The sloped shape can reduce the resistance offered by the tissue of the patient as it slides against the appendage 118 during the insertion of the lead electrode assembly 100 into the patient.
In alternate embodiments, the [0292] proximal edge 129 of the tube formed by the appendage 118 is closed. In one embodiment, the proximal edge 129 of the appendage 118 is closed by a cap (not shown). In another embodiment, the proximal edge 129 of the appendage 118 is closed with stitching placed between the first fin area 612 and the second fin area 615 only at the proximal edge 129 of the appendage 118. In another embodiment, the proximal edge 129 of the appendage 118 is closed by any other means known in the art for this purpose.
FIG. 24([0293] b) illustrates a top plan view of the embodiment illustrated in FIGS. 24(a)-24(b).
FIGS. [0294] 25(a)-25(d) illustrate an alternative embodiment of the lead electrode assembly 100. This embodiment is substantially similar to the embodiment illustrated in FIGS. 15(a)-15(b). The backing layer 130 of this embodiment, however, lacks an integrated fin 120.
FIG. 25([0295] a) illustrates a front plan view of the lead electrode assembly. The fin 120 in this embodiment comprises a fin head 700 and flexible joining material 702.
The [0296] fin head 700 comprises a rectangular sheet having a first face 705, a second face 706, a first end 710 and a second end 712. The fin head 700 further comprises a height measured along the first face 705 between the first end 710 and the second end 712 and a length measured perpendicular to its height.
The [0297] fin head 700 is made of rigid silicone, which has a high durometer. In alternate embodiments, the fin head 700 is composed of any rigid bio-compatible material, such as a rigid bio-compatible polymeric material.
The flexible joining [0298] material 702 comprises a rectangular sheet having a first face 720, a second face 721, a first end 718 and a second end 719. The flexible joining material 702 further comprises a height measured along the first face between the first end 718 and the second end 719. The flexible joining material 702 also comprises a length measured perpendicular to its height. The length of the flexible joining material 702 is the same as the length of fin head 700.
The [0299] second end 712 of the second face 706 of the fin head 700 is attached to the first end 718 of the first face 720 of the flexible joining material 702. The fin head 700 is attached to the flexible joining material 702 with stitching 725. The second end 719 of the first face 720 of the flexible joining material 702 is attached to the first surface 131 of the backing material 130. The flexible joining material 702 is attached to the backing material 130 with stitching 730.
The flexible joining [0300] material 702 is made of flexible silicone. It will be recognized by one skilled in the art, however, that the flexible joining material 702 may be made from many other flexible materials, such as a flexible polymeric material.
FIG. 25([0301] b) illustrates a property of the fin 120. When pressure is applied perpendicular to the first surface 705 of the fin head 205, the fin 120 folds as shown. When the fin 120 folds, its appendage height, H_Appendage, is reduced. This can be seen by a comparison between FIG. 25(a), which shows the fin 120 in an upright position and FIG. 25(b) which shows the fin 120 in a folded position.
FIG. 25([0302] c) illustrates a top planar view of the lead electrode assembly 100 of the embodiment illustrated in FIGS. 25(a) and 25(b). Neither the corners of the electrode 107 nor the corners 735 of the backing layer 130 of this embodiment are rounded. In an alternate embodiment, both the corners of the electrode 107 and the corners 735 of the backing layer 130 of this embodiment are rounded.
FIG. 26 illustrates an alternative embodiment of the [0303] lead electrode assembly 100. This embodiment is substantially similar to the embodiment illustrated in FIGS. 25(a)-25(d). The backing layer 130 of this embodiment, however, lacks a fin head 700 and flexible joining material 702.
Moreover, the [0304] appendage 118 in this embodiment comprises a tube 740 having an interior 755, an exterior 756, a proximal end 757 and a distal end 758. The tube comprises a sheet of material 750. The sheet of material 750 is substantially rectangular having a first pair of sides 751, a second pair of sides 752, a first surface 753 and a second surface 754.
The sheet of [0305] material 750 is folded so that its first pair of sides 751 abut each other. The folded sheet of material 750 forms a tube 740. The first surface 753 of the sheet of material 750 faces the interior 755 of the tube 740. The second surface 754 of the sheet of material 750 faces the exterior of the tube 756. In folding the sheet of material 750 so that the first pair of sides 751 abut each other, the second pair of sides 752 of the sheet of material 750 are folded in a circular shape to form the proximal end 757 and distal end 758 of the tube 740. This results in the tube 740 having a cylindrical shape. The diameter of the circular proximal end 757 and distal end 758 of the tube 756 is approximately 5 mm. In alternate embodiments, the diameter range between approximately 1 mm and approximately 10 mm. The length of the tube 756 as measured between the proximal end 757 and distal end 758 of the tube 756 is approximately 1 cm. In alternate embodiments, length of the tube 756 ranges between approximately 2 mm and approximately 6 cm. In one embodiment, the tube 756 is substantially as long as the electrode 107.
The [0306] second surface 754 of the sheet of material 750 is attached to the first surface 131 of the backing layer 130. The first pair of sides 751 of the sheet of material 750 are attached to the backing layer 130 with stitching 760.
In alternate embodiments, the [0307] proximal end 757 of the tube 740 is closed. In one embodiment, the proximal end 757 of the tube 740 is closed by a cap (not shown). In another embodiment, the proximal end 757 of the tube 740 is closed by holding one of the second pair of sides 752 of the sheet of material 750 closed with stitching. In another embodiment, the proximal end 757 of the tube 740 is closed by any other means known in the art for this purpose.
It should be noted that the [0308] appendage 118 in some alternative embodiments comprises a tube with a shape other than a cylinder. An example of a tube with a shape other than cylindrical is illustrated below in FIG. 27. 5
FIG. 27 illustrates an alternative embodiment of the [0309] lead electrode assembly 100. This embodiment is substantially similar to the embodiment illustrated in FIG. 26. The tube 740 comprising a sheet of material 750, however, is absent from this embodiment.
Moreover, the [0310] appendage 118 of this embodiment comprises a tube 770 having an interior 755 an exterior 756, a proximal end 757 and a distal end 758. The tube comprises a first sheet of material 775, a second sheet of material 776 and a third sheet of material 777. The first sheet of material 775, the second sheet of material 776 and the third sheet of material 777 are all substantially rectangular in shape. Each comprises a first pair of sides 784, a second pair of sides 786, a first surface 788 and a second surface 789. The first pair of sides 784 of each sheet of material are parallel to each other. In another embodiment, the first pair of sides 784 of each sheet of material are non-parallel. The second pair of sides 786 of each sheet of material are parallel to each other. In another embodiment, the second pair of sides 786 of each sheet of material are non-parallel.
The first pairs of [0311] sides 784 of each sheet of material are attached to the first pair of sides 784 of the other sheets of material. In this way the second pair of sides 786 of the first sheet of material 775, the second sheet of material 776 and the third sheet of material 777 form a triangular shaped proximal end 757 and distal end 758 of the tube 770. The sheets of material are attached to each other such that the second surface 789 of each sheet of material faces the interior 755 of the tube 770. The sheets of material are attached to each other with stitching 791.
The height of the [0312] tube 770 is approximately 5 mm. In alternate embodiments, the height ranges between approximately 1 mm and approximately 10 mm. The length of the tube 770 as measured between the proximal end 757 and distal end 758 of the tube 770 is approximately 1 cm. In alternate embodiments, length of the tube 770 ranges between approximately 2 mm and approximately 6 cm. In one embodiment, the tube 770 is substantially as long as the electrode 107.
The second sheet of [0313] material 776 is attached to the backing layer 130 with stitching 790. The first surface 788 of the second sheet of material 776 is positioned next to the first surface 131 of the backing layer 130.
In alternate embodiments, some or all of the sheets of material are reinforced with a layer of Dacron® polymer mesh. In one embodiment, the Dacron® polymer mesh is attached to the [0314] first surface 788 of each sheet of material. In another embodiment, the Dacron® polymer mesh is attached to the second surface 789 of each sheet of material. In another embodiment, the sheets of material are similarly reinforced with a layer of any polymeric material.
In alternate embodiments, the [0315] proximal end 757 of the tube 770 is closed. In one embodiment, the proximal end 757 of the tube 770 is closed by a cap. In another embodiment, the proximal end 757 of the tube 770 is closed by holding the sides 786 of the first sheet of material 775, the second sheet of material 776 and the third sheet of material 777 that form the proximal end 757 of the tube 770 together with stitching. In another embodiment, the proximal end 757 of the tube 770 is closed by any other means known in the art for this purpose.
FIGS. [0316] 28(a)-28(d) illustrate various possible positions for the appendage 118 relative to the lead 21 of the lead electrode assembly 100. Additionally, up to this point, all embodiments of the electrode 107 illustrated and discussed have had a rectangular shape. These figures illustrate alternative embodiments with electrodes 107 of different shapes.
At this point, it is useful to set out two definitions in order to discuss the possible orientation of [0317] appendages 118.
The interface line is defined as the center line of the [0318] appendage 118 as traced on the electrode 107. FIG. 28(a) illustrates the interface line 800 of the appendage 118 of a lead electrode assembly 100.
The line of the lead is defined as the line along which the [0319] lead 21 of the lead electrode assembly 100 enters the lead fastener 146. The line of the lead 805 of line 21 is shown as it enters the lead fastener 146 (in phantom). As the lead 21 approaches the lead fastener 146, the closest section 807 of the lead 21 forms the line of the lead. When the lead 21 is not bent, the entire lead 21 lies along the line of the lead.
FIG. 28([0320] b) illustrates an embodiment wherein the lead 21 is not bent and the entire lead 21 lies along the line of the lead 805.
The electrode length, L[0321] _Electrode, is the length of the electrode 107 as measured along the interface line 800.
In the embodiments of the [0322] lead electrode assembly 100 shown in FIGS. 28(b) and 28(c), the interface line 800 is the same line as the line of the lead 805. In the embodiment shown in FIG. 28(a) the interface line 800 is parallel with the line of the lead 805.
In the embodiment of the [0323] lead electrode assembly 100 shown in FIG. 28(d), the interface line 800 intersects the lead fastener 146 (phantom view).
FIGS. [0324] 28(e)-28(h) show various additional electrode shapes disposed in various lead electrode assemblies 100. The electrode shapes are not limited, however, to the shapes specifically illustrated.
The [0325] electrode 204 depicted in FIG. 28(e) has a “thumbnail” shape. The proximal end 104 of this electrode 107 is generally rounded. As the electrode 107 moves distally along its length, the conductive surface terminates at the distal end 103 of the electrode 107.
An ellipsoidal shaped [0326] electrode 107 is depicted in FIG. 28(f). The proximal end 104 of the ellipsoidal shaped electrode 107 is generally rounded. As the ellipsoidal shaped electrode 107 moves distally along its length, the conductive surface terminates in a rounded distal end 103.
A circular shaped [0327] electrode 107 is illustrated in FIG. 28(g).
A triangular shaped [0328] electrode 107 is depicted in FIG. 28(h). Triangular shaped electrodes 107 also incorporate electrodes that are substantially triangular in shape. In particular to FIG. 28(h), the corners of the triangular shaped electrode 107 are rounded.
Several lead electrode [0329] assembly manipulation tools 927 have been developed to manipulate the lead electrode assemblies during their surgical implantation.
FIG. 29 illustrates an embodiment of a lead electrode [0330] assembly manipulation tool 927. The lead electrode assembly manipulation tool 927 comprises an enhanced hemostat 930 used to manipulate lead electrode assemblies 100 comprising an eyelet during their implantation in patients.
The enhanced [0331] hemostat 930 comprises the following components: a hemostat having a first prong 931, a second prong 932, a hinge 939 and an eyelet pin 940. The first prong 931 is attached to the second prong 932 by the hinge 939. The eyelet pin is attached to the second prong 932.
The [0332] first prong 931 comprises a first end 933 and a second end 934. The second prong 932 comprises a first end 935 and a second end 936. The first prong and second prong are approximately 75 cm long and curved with a radius of approximately 30 cm. In alternate embodiments, the curvature of the hemostat does not have a radius of approximately 30 cm, but instead approximates the curvature of the thorax of a patient. In one embodiment, the curvature of the hemostat approximates the curvature of the thorax of a patient along a subcutaneous path taken from the anterior axillary line, posteriorly toward the spine.
The [0333] first prong 931 is pivotally attached to the second prong 932 by the hinge 939. The hinge is attached to the first prong 931 approximately 10 cm from the first end 933. In this embodiment, the hinge is attached to the second prong 932 approximately 10 cm from the second end 935.
The [0334] eyelet pin 940 can be inserted through the eyelet 301 of a fin 120 of the lead electrode assembly 100 such as the lead electrode assembly 100 discussed with reference to FIG. 17(a)-17(g) as a means of capturing the lead electrode assembly 100 prior to its implantation in a patient.
The [0335] eyelet pin 940 is a cylindrical member having a first end 941 and a second end 942. In an alternate embodiment, the eyelet pin 940 is a hook-shaped member. The diameter of the cylinder is approximately 2 mm. In alternate embodiments, the diameter of the cylinder ranges from approximately 1 mm to approximately 5 mm. The length of the eyelet pin 940 is approximately 8 mm. In alternate embodiments, the length of the eyelet pin 940 ranges from approximately 4 to approximately 15 mm.
The first end of the [0336] eyelet pin 940 is attached to the second prong 932, approximately 8 mm from the second end 936 of the second prong 932. In alternate embodiments, the eyelet pin 940 is attached to the second prong 932 at various lengths from the second end 936 of the second prong 932.
The [0337] eyelet pin 940 is attached to the second prong 932 in an orientation perpendicular to the length of the second prong 932. The eyelet pin 940 is attached to the second prong 932 so that it extends away from the second end 934 of the first prong 931.
In this embodiment, all of the components are made of stainless steel. In an alternative embodiment, some or all of the components are composed metals other than stainless steel or are composed of a polymeric material. [0338]
We now turn to a discussion of the positions of the components that comprise an entire S-ICD system including the [0339] lead electrode assembly 100 when it is implanted in a patient.
FIGS. [0340] 30(a) and 30(b) illustrate an embodiment of the S-ICD system implanted in a patient as a means of providing cardioversion/defibrillation energy.
FIG. 30([0341] a) is a perspective view of a patient's ribcage with an implanted S-ICD system. The S-ICD canister 11 is implanted subcutaneously in the anterior thorax outside the ribcage 1031 of the patient, left of the sternum 920 in the area over the fifth rib 1038 and sixth rib 1036. The S-ICD canister 11, however, may alternately be implanted anywhere over the area between the third rib and the twelfth rib. The lead 21 of the lead electrode assembly 100 is physically connected to the S-ICD canister 11 where the transthoracic cardiac pacing energy or effective cardioverion/defibrillation shock energy (effective energy) is generated. The term “effective energy” as used in this specification can encompass various terms such as field strength, current density and voltage gradient.
The [0342] lead 21 of the lead electrode assembly 100 travels from the S-ICD canister 11 to the electrode 107, which is implanted subcutaneously in the posterior thorax outside the ribcage 1031 of the patient in the area over the eighth rib 1030 and ninth rib 1034. The electrode 107, may alternately be implanted subcutaneously anywhere in the posterior thorax outside the ribcage 1031 of the patient in the area over the third rib 1030 and the twelfth rib 1034. The bottom surface 115 of the electrode 107 faces the ribcage. The electrode or active surface 15 (phantom view) of the canister 11 also faces the ribcage.
FIG. 30([0343] b) is a cross-sectional side plan view of the patient's rib cage. Here it is seen that the lead 21 travels around the circumference of the thorax, in the subcutaneous layer beneath the fat 1050 between the outside of the ribcage 1031 and the skin 1055 covering the thorax.
We now turn to a discussion of a method by which the [0344] lead electrode assembly 100 of the S-ICD system is implanted in a patient using a standard hemostat as well as the enhanced hemostat described above. FIG. 31 and FIGS. 32(a)-32(d) illustrate aspects of this method.
In operation, as seen in FIG. 31, an [0345] incision 905 is made in the patient 900 in the anterior thorax between the patient's third and fifth rib, left of the sternum 920. The incision can alternately be made in any location between the patient's third and twelfth rib. The incision can be made vertically (as shown), horizontally or angulated. In order to minimize scarring, the incision can be made along Langher's lines.
FIG. 32([0346] a) shows a bottom view cross-section of the patient 900, along the line 32(a) shown in FIG. 31. A hemostat 930, with prongs 932 is introduced into the incision 905. The hemostat 930 is inserted with its prongs together without anything gripped between them. The prongs 932 of the hemostat 930 are pushed through the fat 1050 between the skin 1055 of the thorax and the ribcage 1031 to create a subcutaneous path 1090. The prongs 932 of the hemostat 930 can alternately be pushed beneath the fat 1050 that lies between the skin 1055 of the thorax and the ribcage 1031 to create a subcutaneous path 1090 between the fat 1050 and the ribcage 1031.
The hemostat is moved around the [0347] ribcage 1031 until the subcutaneous path 1090 reaches within approximately 10 cm of the spine 1035 between the eighth rib 1030 and ninth rib 1034 (this location is best seen in FIG. 30(a)) between the skin 1055 and the ribcage 1031. The subcutaneous path 1090 can alternately be made to reach any location between the skin 1055 and the ribcage 1031 between the patient's third and twelfth rib. The hemostat 930 is then withdrawn. Alternately, the hemostat 930 can be moved around the ribcage 1031 until the subcutaneous path 1090 terminates at a termination point 1085 at which a line 1084 drawn from the termination point 1085 to the incision 905 would intersect the heart 910.
Next, as shown in FIG. 32([0348] b), the appendage 118 of a lead electrode assembly 100, is squeezed between the tongs 932 of a hemostat 930.
As shown in FIG. 32([0349] c), the lead electrode assembly 100 and hemostat tongs 932 are introduced to the subcutaneous path 1090 and pushed through the subcutaneous path until the lead electrode assembly 100 reaches the termination point 1085 of the path. The appendage 118 of the lead electrode assembly 100 is then released from the tongs 932 of the hemostat 930. The hemostat 930 is then withdrawn from the subcutaneous path 1090.
In an alternative method, the [0350] enhanced hemostat 930 seen in FIG. 29 is used to introduce the lead electrode assembly 100 into the subcutaneous path 1090 created as discussed above. After the subcutaneous path 1090 is created, the lead electrode assembly 100 is attached to the enhanced hemostat 930 as shown in FIG. 32(d). Eyelet pin 1108 is inserted through the eyelet 301 in the fin 120 of the lead electrode assembly 100. The enhanced hemostat 930 is then used to introduce the lead electrode assembly 100 into the subcutaneous path 1090, as shown in FIG. 32(c). The lead electrode assembly 100 is then moved through the subcutaneous path 1090 until the electrode 107 reaches the end of the path 1085. The enhanced hemostat 930 is then moved until the lead electrode assembly 100 is released from the eyelet pin 940. The enhanced hemostat 930 is then withdrawn from the subcutaneous path 1090.
FIGS. [0351] 33(a)-33(c) illustrate an alternative embodiment of the lead electrode assembly 100. This embodiment is substantially similar to the embodiments illustrated in FIGS. 17(a)-17(g). The backing layer 130 of this embodiment, however, lacks an integrated fin tab 180. Moreover, the appendage 118 of the lead electrode assembly 100 of this embodiment comprises a rail 1100.
FIG. 33([0352] a) illustrates the rail 1100 of the lead electrode assembly 100 of this embodiment. The rail 1100 is a member attached to the electrode 107 that can be captured by a lead electrode assembly manipulation tool and used to precisely locate the electrode 107 during its surgical implantation within the patient. The rail 1100 comprises three sections: a foundation 1105, a riser 1110 and a head 1115. The foundation 1105 is separated from the head 1115 by the riser 1125.
The [0353] foundation 1105 comprises a flat, substantially planar member, comprising a first pair of sides 1106 and a second pair of sides 1107. The first pair of sides 1106 of the foundation 1105 are substantially linear and substantially parallel. In an alternate embodiment, the first pair of sides 1106 of the foundation 1105 are neither linear nor parallel. The length of the first pair of sides 1106 of the foundation 1105 is approximately 2 cm. In alternate embodiments, the length of the first pair of sides 1106 of the foundation 1105 ranges from approximately 2 mm to approximately 6 cm. In an alternate embodiment, the first pair of sides 1106 of the foundation 1105 are as long as the electrode 107 (not shown) of the lead electrode assembly 100 (not shown).
The second pair of [0354] sides 1107 of the foundation 1105 are substantially linear and substantially parallel. In an alternate embodiment, the second pair of sides 1107 of the foundation 1105 are neither linear nor parallel. The length of the second pair of sides 1107 of the foundation 1105 is approximately 1 cm. In alternate embodiments, the length of the second pair of sides 1107 of the foundation 1105 ranges from approximately 0.5 cm to approximately 3 cm.
The [0355] foundation 1105 further comprises a top surface 1120 and a bottom surface 1121. The foundation 1105 has a thickness, measured as the distance between the top surface 1120 and the bottom surface 1121. The thickness of the foundation 1105 is 2 mm. In alternate embodiments, the thickness of the foundation 1105 ranges between approximately 1 mm and approximately 5 mm.
Turning now to the [0356] riser 1110, the riser 1110 comprises a flat, substantially planar protrusion from the top surface 1120 of the foundation 1105 of the rail 1100. The riser comprises a first face 1125, a second face 1126, a top 1127, a bottom 1128, a proximal end 1123 and a distal end 1124. The first face 1125 and second face 1126 are parallel to each other and perpendicular to the top surface 1120 of the foundation 1105. The first face 1125 and a second face 1126 of the riser 1110 are parallel to the first pair of sides 1106 of the foundation 1105. The bottom 1128 of the riser 1110 joins the foundation 1105 in a position centered between the first pair of sides 1106 of the foundation 1105. The proximal end 1123 of the riser 1110 and the distal end 1124 of the riser 1110 are parallel to each other and perpendicular to the top surface 1120 of the foundation 1105. In other embodiments, the proximal end 1123 of the riser 1110 and the distal end 1124 of the riser 1110 are not parallel to each other.
In one embodiment, the [0357] proximal end 1123 of the riser 1110 is not perpendicular the top surface 1120 of the foundation 1105. Instead, the proximal end 1123 of the riser 1110 is sloped, so that the proximal end 1123 and the distal end 1124 of the riser 1110 are closer at the top 1127 of the riser 1110 than at the bottom 1128 of the riser. A slanted proximal end 1123 make the rail 1100 of the lead electrode assembly 100 offer less resistance against the tissues of the patient during insertion into the patient.
The height of the riser, H[0358] _Riser, is measured as the distance 11 between the top surface 1120 of the foundation 1105 to the head 1115, perpendicular to the top surface 1120 of the foundation 1105. The height of the riser is approximately 5 mm. In alternate embodiments, the height of the riser ranges from approximately 1 mm to approximately 10 mm.
The [0359] riser 1110 has a width, measured as the distance between the first face 1125 and the second face 1126. The width of the riser 1110 is 2 mm. In alternate embodiments, the width of the riser 1110 ranges from approximately 1 mm to approximately 6 mm.
Turning now to the [0360] head 1115, the head 1115 is a flat, substantially planar member. The head 1115 comprises a first pair of sides 1136, a second pair of sides 1137, a top surface 1116 and a bottom surface 1117 (not shown). The first pair of sides 1136 and the second pair of sides 1137 of the head 1115 are substantially linear and substantially parallel. In an alternate embodiment, the first pair of sides 1136 of the head 1115 are neither linear nor parallel. In an alternate embodiment, the second pair of sides 1137 of the head 1115 are neither linear nor parallel.
The length of the first pair of [0361] sides 1136 of the head 1115 is equal to the length of the first pair of sides 1106 of the foundation 1105. In alternate embodiments, the length of the first pair of sides 1136 of the head 1115 is unequal to the length of the first pair of sides 1106 of the foundation 1105. The length of the second pair of sides 1137 of the head 1115 is approximately 5 mm. In alternate embodiments, the length of the second pair of sides 1137 of the head 1115 ranges from approximately 3 mm to approximately 10 mm.
The [0362] bottom surface 1117 of the head 1115 joins the top 1127 of the riser 1110 opposite the foundation 1105 of the rail 1100. The top surface 1116 and the bottom surface 1117 of the head 1115 are parallel to the top surface 1120 of the foundation 1105. In an alternate embodiment, the top surface 1116 and the bottom surface 1117 of the head 1115 are not parallel to the top surface 1120 of the foundation 1105.
The [0363] head 1115 has a thickness, measured as the distance between the top surface 1116 and the bottom surface 1117 of the head 1115. The thickness of the head 1115 is approximately 2 mm. In alternate embodiments, the thickness of the head ranges between approximately 2 mm and approximately 10 mm.
The [0364] foundation 1105, the head 1115 and the riser 1110 are made of stainless steel. In alternate embodiments, some or all of the sections of the rail 1100 are made of metals other than stainless steel. In alternate embodiments, some or all of the sections of the rail 1100 are made of a polymeric material wherein the polymeric material is selected from the group consisting essentially of a polyurethane, a polyamide, a polyetheretherketone (PEEK), a polyether block amide (PEBA), a polytetrafluoroethylene (PTFE), a silicone and mixtures thereof.
The [0365] foundation 1105, the head 1115 and the riser 1110 are machined from the same piece of material. In an alternate embodiment, some or all of the sections are formed independently and welded to the others.
Turning in detail to FIG. 33([0366] b), the position of the rail 1100 within the lead electrode assembly 100 will be discussed. The rail 1100 is positioned so that its bottom surface 1121 is adjacent to and covers a region of the first surface 131 of the backing layer 130. The rail is centered between the first side 133 and second side 134 of the backing layer 130. In an alternate embodiment, the rail is not centered between the first side 133 and second side 134 of the backing layer 130.
In an alternate embodiment, there is no [0367] backing layer 130 and the rail 1100 is positioned so that its bottom surface 1121 is adjacent to the top surface 110 of the electrode 107.
Turning now to the [0368] electrode 107 of this embodiment, the electrode 107 is the same shape and size as the electrode 107 discussed with reference to FIGS. 17(a)-(g). In alternative embodiments, the length of the first pair of sides 108 (not shown) and second pair of sides 109 (not shown) of the electrode 107 range independently between approximately 1 cm and approximately 5 cm.
Turning now to the molded [0369] cover 220, the skirt 222 of the molded cover 220 partially covers the bottom surface 115 of the electrode 107 as discussed with reference to FIG. 17(d). The molded cover 220 further substantially covers the first surface 131 of the backing layer 130. The molded cover 220 does not cover the first surface 131 of the backing layer 220 in the region in which the bottom surface 1121 of the rail 1100 is adjacent to the backing layer 130. Instead, the molded cover 220 in this region substantially covers the top surface 1120 of the rail 1100. The molded cover 220 abuts the first face 1125 and second face 1126 of the riser 1110 of the rail 1100.
Turning to FIG. 33([0370] c), the position of the lead 21 and the appendage 118 will now be discussed. The interface line 800 of the appendage 118 and the line of the lead 805 are the same line. In an alternate embodiment, interface line 800 of the appendage 118 and the line of the lead 805 are not the same line. The line of the lead 805 is centered between the first pair of sides 108 (phantom view) of the electrode 107 (phantom view). In an alternate embodiment, the line of the lead 805 is not centered between the first pair of sides 108 of the electrode 107.
FIG. 34 illustrates an alternative embodiment of the [0371] lead electrode assembly 100. This embodiment is substantially similar to the embodiment illustrated in FIGS. 33(a)-33(c). In this embodiment, however, the dimensions of the electrode 107 are different from those of the embodiment illustrated in FIGS. 33(a)-33(c).
The first pair of [0372] sides 108 of the electrode 107 (phantom view) are approximately 2.4 cm in length. The second pair of sides 109 of the electrode 107 are approximately 4 cm in length. In alternative embodiments, the length of the first pair of sides 108 and second pair of sides 109 of the electrode 107 range independently between approximately 1 cm and approximately 5 cm.
The [0373] interface line 800 of the rail 1100 is parallel to the line of the lead 805. In an alternate embodiment, the interface line 800 of the rail 1110 is not parallel to the line of the lead 805. The interface line 800 of the rail 1100 is centered between the first pair of sides 108 of the electrode 107. In an alternate embodiment, the interface line 800 of the rail 1100 is not centered between the first pair of sides 108 of the electrode 107.
The line of the [0374] lead 805 is not centered between the first pair of sides 108 of the electrode 107. Because the lead 805 is not centered between the first pair of sides 108 of the electrode 107, the lead rail 1110 may be more easily accessed by a lead electrode manipulation tool (not shown). In an alternate embodiment, the line of the lead 805 is centered between the first pair of sides 108 of the electrode 107.
FIG. 35 illustrates a lead electrode [0375] assembly manipulation tool 927 useful for manipulating a lead electrode assembly (not shown) having an appendage 118 comprising a rail 1100 during the implantation of the lead electrode assembly 100 in a patient. Examples of such lead electrode assembly 100 embodiments are shown in FIGS. 33(a)-33(c) and 34.
The lead electrode [0376] assembly manipulation tool 927 comprises a handle 1142, a rod 1144 and a rail fork 1146. The handle 1142 i s connected to the rod 1144. The rail fork 1146 is also connected to the rod 1144.
The [0377] rod 1144 is a cylindrical member with a diameter of approximately 4 mm, approximately 25 cm in length, having a proximal end 1147 and a distal end 1148. The rod 1144 is curved with a radius of approximately 20 cm.
The rod is made of steel. In other embodiments, the rod is composed of titanium, a polymeric material or any other material suitable for this purpose. [0378]
The [0379] handle 1142 is a cylindrical member with a diameter sized to fit comfortably in the palm of a surgeon's hand. The rod is connected to the proximal end 1147 of the rod 1144. In an alternate embodiment, the handle 1142 is not cylindrical. In an alternate embodiment, the handle 1142 has ergodynamic contours.
The handle is made of polyurethane. In an alternate embodiment, the handle is made of any metal, or any polymeric material suitable for this purpose. [0380]
Turning now to FIG. 35([0381] b), the rail fork 1146 is attached to the distal end 1148 of the rod 1144. The rod further comprises a slot 1162 in its distal end. The rail fork comprises a pair of tines 1151 separated by a gap 1153 and a tine base 1160 having a tang 1161.
Each of the pair of [0382] tines 1151 has a proximal end 1154 and a distal end 1155. The proximal ends 1154 of the pair of tines 1151 are attached to the tine base 1160. Each of the pair of tines 1151 has a substantially rectangular form with straight inner sides 1156 and straight outer sides 1157. The distal ends 1155 of each of the pair of tines 1151 are rounded. The length of the pair of tines 1151, measured from the distal end 1155 to the proximal end 1154, is substantially equal to the length of the first pair of sides 1106 of the rail 1100 of the lead electrode assembly 100. In alternate embodiments, the length of the pair of tines 1151 is substantially greater than or less than the length of the first pair of sides 1106 of the rail 1100.
The pair of [0383] tines 1151 are separated by a gap 1153 formed by the inner sides 1156 of the pair of tines 1151 and the tine base 1160.
The pair of [0384] tines 1151 and the tine base 1160 comprising the rail fork 1146 are punched from a single sheet of steel having a thickness of approximately 3 mm. In other embodiments, the rail fork 1146 is composed of titanium, a polymeric material or any other material suitable for this purpose. In one embodiment, the handle 1142, the rod 1144 and the rail fork 1146 are all made from the same piece of material.
FIG. 35([0385] c) illustrates a side plan view of the lead electrode assembly manipulation tool 927. The rod 1144 further comprises a slot 1162 in its distal end 1148. The tine base 1160 connects the pair of tines 1151 to the distal end 1148 of the rod 1144. The tine base 1160 comprises a tang 1161 (phantom view). The tang 1161 is inserted in the slot 1162 in the rod 1144. The tang 1161 is welded in the slot 1162 of the rod 1144.
We now turn to a description of the use of the lead electrode [0386] assembly manipulation tool 927 in the implantation of a lead electrode assembly 100 into a patient.
As discussed with reference to FIG. 31, an [0387] incision 905 is made in the patient 900. As discussed with reference to FIG. 32(a), a subcutaneous path 1090 is created in the patent 900 with a hemostat 932.
As shown in FIG. 35([0388] d), the lead electrode assembly 100 is then captured by the lead electrode assembly manipulation tool 927. The rail 1110 of the lead electrode assembly 100 is inserted into the rail fork 1146 of the lead electrode assembly manipulation tool 927. The riser 1110 (phantom view) of the rail is placed into the gap 1153 between the pair of tines 1151 of the rail fork 1146. The pair of tines 1151 fit between the bottom surface 1117 of the head 1115 of the rail 1100 and the molded cover 220. The rail 1100 is slid toward the proximal end 1155 of the pair of tines 1151 until the riser 1110 of the rail 1100 reaches the tine base 1160 of the rail fork 1146. The lead 21 of the lead electrode assembly 100 can then be pulled in toward the handle 1142 of the lead electrode assembly manipulation tool 927 until it is taught. This acts to prevent the rail 1100 of the lead electrode assembly 100 from sliding toward the distal end 1151 of the pair of tines 1151 of the rail fork 1146.
As discussed with reference to FIG. 32([0389] c), the lead electrode assembly manipulation tool 927 may then be used to place the lead electrode assembly 100 into the incision 905 of the patient 900 and used to move the electrode 107 to the termination point 1085 of the subcutaneous path 1090.
The [0390] lead electrode assembly 100 is then released from the lead electrode assembly manipulation tool 927. To achieve this, the lead 21 of the lead electrode assembly 100 is released so that the pair of tines 1151 of the rail fork 1146 of the lead electrode assembly manipulation tool 927 can slide relative to the rail 1100 of the lead electrode assembly 100. The lead electrode assembly manipulation tool 927 may then be extracted from the subcutaneous path 1090, leaving the lead electrode assembly 100 behind.
FIGS. [0391] 36(a)-36(b) illustrate an alternative embodiment of the lead electrode assembly 100. This embodiment is substantially similar to the embodiments illustrated in FIGS. 17(a)-17(g). The backing layer 130 of this embodiment, however, lacks an integrated fin tab 180. Moreover, the lead electrode assembly 100 of this embodiment further comprises a pocket 1300.
FIG. 36([0392] a) illustrates a cross-sectional side plan view of this embodiment. The pocket 1300 comprises a layer of material 1315 and stitching 360. The pocket further comprises an interior 1305 and an opening 1310. The layer of material 1315 is attached to the molded cover 220 with the stitching 360. The molded cover 220 is, in turn, attached to the electrode 107.
The molded [0393] cover 220 comprises an outer surface 1330 and a top surface 1331. The outer surface 1330 of the molded cover 220 is the surface of the molded cover 220 that does not lie adjacent to the backing layer 131 or the electrode 107. The top surface 1331 of the molded cover 220 faces away from, and parallel to the electrode 107.
The layer of [0394] material 1315 of the pocket 1300 comprises an inner face 1316 and an outer face 1317. The layer of material 1315 is attached to the top surface 1331 of the molded cover 220 so that the inner face 1316 of the layer of material 1315 faces the top surface 1331 of the molded cover 220. The inner face 1316 of the layer of material 1315 also faces the top surface 110 of the electrode 107.
The layer of [0395] material 1315 is made of polyurethane. In other embodiments, the layer of material 1315 is made of any bio-compatible material suitable for this purpose. In other embodiments, the layer of material 1315 is made of any bio-compatible polymeric material.
The [0396] stitching 360 fastening the layer of material 1315 to the top surface 1331 of the molded cover 220 is comprised of nylon. In alternate embodiments, the stitching 360 comprises any polymeric material.
FIG. 36([0397] b) illustrates a top plan view of the lead electrode assembly 100 of FIG. 36(a). The top surface 1331 of the molded cover 220 has a first side 1333, a second side 1334, a distal end 1336, a proximal end 1337, a length and a width. The distal end 1336, proximal end 1337, first side 1333 and second side 1334 of the top surface 1331 of the molded cover 220 are positioned substantially over the distal end 137 (phantom view), proximal end 138 (phantom view), first side 133 (not shown) and second side 134 (not shown) of the backing layer 130 (phantom view) respectively.
The width of the [0398] top surface 1331 of the molded cover 220 is measured as the distance between the first side 1333 and second side 1334 of the back surface. The length of the top surface 1331 of the molded cover is measured as the distance between the distal end 1336 and proximal end 1337 of the molded cover 220.
The layer of [0399] material 1315 comprises a periphery 1318 and a middle portion 1319. More particularly, the layer of material 1315 comprises a distal end 1320, a proximal end 1321, a first side 1322 and a second side 1323. The periphery 1318 of the layer of material 1315 comprises the distal end 1320, the proximal end 1321, the first side 1322 and the second side 1323 of the layer of material 1315. The middle portion 1319 of the layer of material 1315 comprises the area between the distal end 1320, the proximal end 1321, the first side 1322 and the