US20020107549A1 - Subcutaneous electrode with improved contact shape for transthorasic conduction - Google Patents

Abstract

One embodiment of the present invention provides a lead electrode assembly for use with an implantable cardioverter-defibrillator subcutaneously implanted outside the ribcage between the third and twelfth ribs comprising an electrode.

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. 09/663,607, filed Sep. 18, 2000, pending, and U.S. patent application entitled “UNITARY SUBCUTANEOUS ONLY IMPLANTABLE CARDIOVERTER-DEFIBRILLATOR AND OPTIONAL PACER,” having Ser. No. 09/663,606, filed Sep. 18, 2000, pending, and U.S. patent application entitled “SUBCUTANEOUS ELECTRODE WITH IMPROVED CONTACT SHAPE FOR TRANSTHORACIC CONDUCTION,” filed Aug. 27, 2001, pending, of which all applications are assigned to the assignee of the present application, and the disclosures of all applications are hereby incorporated by reference.[0001]
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 non-transvenous system.[0002]
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. Shocks used for defibrillation therapy can comprise a biphasic truncated exponential waveform. As for pacing, a constant current density is desired to reduce or eliminate variability due to the electrode/tissue interface.[0003]
• Defibrillation/cardioversion systems include body implantable electrodes that are connected to a hermetically sealed container housing the electronics, battery supply and capacitors. The entire system is referred to as implantable cardioverter/defibrillators (ICDs). The electrodes used in ICDs can be in the form of patches applied directly to epicardial tissue, or, more commonly, are on the distal regions of small cylindrical insulated catheters that typically enter the subclavian venous system, pass through the superior vena cava and, into one or more endocardial areas of the heart. Such electrode systems are called intravascular or transvenous electrodes. 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, in combination with other intravascular or transvenous electrodes, or in combination with an epicardial patch or subcutaneous electrodes. 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.[0004]
• 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 no practical use. It has in fact never been used because of the surgical difficulty of applying such a device ([0005]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.[0006]
• 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.[0007]
• 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.[0008]
• In addition to the background related to ICD therapy, the present invention requires a brief understanding of a related therapy, the automatic external defibrillator (AED). AEDs employ the use of cutaneous patch electrodes, rather than implantable lead systems, to effect defibrillation under the direction of a bystander user who treats the patient suffering from V-Fib with a portable device containing the necessary electronics and power supply that allows defibrillation. AEDs can be nearly as effective as an ICD for defibrillation if applied to the victim of ventricular fibrillation promptly, i.e., within 2 to 3 minutes of the onset of the ventricular fibrillation.[0009]
• 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.[0010]
• What is needed therefore, especially for children and for prophylactic long term use for those at risk of cardiac arrest, 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.[0011]
SUMMARY OF THE INVENTION
• One embodiment of the present invention provides a lead electrode assembly for use with an implantable cardioverter-defibrillator subcutaneously implanted outside the ribcage between the third and twelfth ribs comprising an electrode.[0012]
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:[0013]
• FIG. 1 is a schematic view of a Subcutaneous ICD (S-ICD) of the present invention;[0014]
• FIG. 2 is a schematic view of an alternate embodiment of a subcutaneous electrode of the present invention;[0015]
• FIG. 3 is a schematic view of an alternate embodiment of a subcutaneous electrode of the present invention;[0016]
• FIG. 4 is a schematic view of the S-ICD and lead of FIG. 1 subcutaneously implanted in the thorax of a patient;[0017]
• 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;[0018]
• FIG. 6 is a schematic view of the S-ICD and lead of FIG. 3 subcutaneously implanted in the thorax of a patient;[0019]
• 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;[0020]
• FIG. 8 is a schematic view of an introducer set for performing the method of lead insertion of any of the described embodiments;[0021]
• 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;[0022]
• FIG. 10 is a schematic view of an alternate embodiment of an S-ICD of the present invention;[0023]
• FIG. 11 is a schematic view of the S-ICD of FIG. 10 subcutaneously implanted in the thorax of a patient;[0024]
• 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[0025]
• 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.[0026]
• FIG. 14 is a schematic view of a Unitary Subcutaneous ICD (US-ICD) of the present invention;[0027]
• FIG. 15 is a schematic view of the US-ICD subcutaneously implanted in the thorax of a patient;[0028]
• FIG. 16 is a schematic view of the method of making a subcutaneous path from the preferred incision for implanting the US-ICD.[0029]
• FIG. 17 is a schematic view of an introducer for performing the method of US-ICD implantation; and[0030]
• 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.[0031]
• FIG. 14([0032]a) is a side plan view of an embodiment of a lead electrode assembly with a top-mounted fin;
• FIG. 14([0033]b) is a top plan view of an embodiment of a lead electrode assembly with a top-mounted fin;
• FIG. 14([0034]c) is a side plan view of a section of the lead in an embodiment of the lead electrode assembly;
• FIG. 14([0035]d) is a cross-sectional view of a filar in the lead in an embodiment of the lead electrode assembly;
• FIG. 14([0036]e) is a cross-sectional view of the lead fastener of an embodiment of a lead electrode assembly;
• FIG. 14([0037]f) is an exploded view of the lead fastener of an embodiment of a lead electrode assembly;
• FIG. 15([0038]a) is a cross-sectional front plan view of an embodiment of a lead electrode assembly with a top-mounted fin;
• FIG. 15([0039]b) is a top plan view of an embodiment of a lead electrode assembly with a top-mounted fin;
• FIG. 16([0040]a) is a perspective view of an embodiment of a lead electrode assembly with a top-mounted fin;
• FIG. 17([0041]a) is a cross-sectional side plan view of an embodiment of a lead electrode assembly with a top-mounted f in and a molded cover;
• FIG. 17([0042]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([0043]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([0044]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([0045]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([0046]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([0047]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([0048]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([0049]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([0050]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;[0051]
• FIG. 20([0052]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([0053]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([0054]c) is a bottom plan view of an embodiment of a lead electrode assembly with a side-mounted fin;
• FIG. 20([0055]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([0056]a) is a side plan view of a lead electrode assembly with a top-mounted loop;
• FIG. 21([0057]b) is a cross-sectional rear plan view of a lead electrode assembly with a top-mounted loop;
• FIG. 21([0058]c) is a top plan view of a lead electrode assembly with a top-mounted loop;
• FIG. 22([0059]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([0060]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([0061]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([0062]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([0063]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([0064]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([0065]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([0066]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([0067]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([0068]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([0069]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. 24([0070]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([0071]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([0072]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;[0073]
• 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;[0074]
• FIGS.[0075]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.[0076]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;[0077]
• FIG. 30([0078]a) is a perspective view of a patient's ribcage showing the orientation of the components in an implanted S-ICD system;
• FIG. 30([0079]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;[0080]
• FIG. 32([0081]a) is a cross-sectional bottom plan view of a patient along line32(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([0082]b) is a perspective view of a lead electrode assembly captured by a custom hemostat;
• FIG. 32([0083]c) is a cross-sectional bottom plan view of a patient along line32(a) of FIG. 31 illustrating the implantation of a lead electrode assembly via the subcutaneous path;
• FIG. 32([0084]d) is a top view of a lead electrode assembly captured by a custom hemostat;
• FIG. 33([0085]a) is a perspective view of a rail of an embodiment of the lead electrode assembly;
• FIG. 33([0086]b) is a cross-sectional front plan view of an embodiment of the lead electrode assembly where the appendage is a rail;
• FIG. 33([0087]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;[0088]
• FIG. 35([0089]a) is a perspective view of a lead electrode assembly manipulation tool with a rail fork;
• FIG. 35([0090]b) is a top plan view of a lead electrode assembly manipulation tool with a rail fork;
• FIG. 35([0091]c) is a side plan view of a lead electrode assembly manipulation tool with a rail fork;
• FIG. 35([0092]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([0093]a) is a cross-sectional side plan view of a lead electrode assembly with a pocket;
• FIG. 36([0094]b) is a top plan view of a lead electrode assembly with a pocket;
• FIG. 36([0095]c) is a cross-sectional side plan view of a lead electrode assembly with a pocket and a fin;
• FIG. 37([0096]a) is a bottom plan view of a lead electrode assembly with a pocket;
• FIG. 37([0097]b) is a top plan view of a lead electrode assembly with a pocket;
• FIG. 38([0098]a) is a top plan view of a lead electrode assembly manipulation tool with a paddle;
• FIG. 38([0099]b) is a side plan view of a lead electrode assembly manipulation tool with a paddle;
• FIG. 38([0100]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([0101]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([0102]b) is a top plan view of a lead electrode assembly with a first channel guide and a second channel guide;
• FIG. 40([0103]a) is a top plan view of a lead electrode assembly manipulation tool with a channel guide fork;
• FIG. 40([0104]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([0105]a) is a perspective view of a subcutaneous implantable cardioverter-defibrillator kit; and
• FIG. 41([0106]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[0107]active canister11 and asubcutaneous electrode13 attached to the canister. The canister has an electricallyactive surface15 that is electrically insulated from theelectrode connector block17 and thecanister housing16 via insulatingarea14. 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 one embodiment, a 100 uF biphasic waveform is used of approximately 10-20 ms total duration and with the initial phase containing approximately ⅔ 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 can be biphasic in one embodiment and similar in pulse amplitude to that used for conventional transthoracic pacing.[0108]
• 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.[0109]
• 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.[0110]
• 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.[0111]
• 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.[0112]
• 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 one embodiment is that the charge time for the therapy, is intentionally left 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.[0113]
• Different[0114]subcutaneous electrodes13 of the present invention are illustrated in FIGS.1-3. Turning to FIG. 1, thelead21 for the subcutaneous electrode is preferably composed of silicone or polyurethane insulation. The electrode is connected to the canister at its proximal end viaconnection port19 which is located on an electricallyinsulated area17 of the canister. The electrode illustrated is a composite electrode with three different electrodes attached to the lead. In the embodiment illustrated, anoptional anchor segment52 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[0115]coil electrode27 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, afirst sense electrode25 is located proximally to the coil electrode and asecond sense electrode23 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 insulatingareas29. 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 twosensing electrodes25 and23 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[0116]sensing electrodes26 and28 are located on the electricallyactive surface15 with electrical insulator rings30 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.[0117]
• 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 and the US-ICD of the present invention uses maximum voltages in the range of about 50 to about 3500 Volts and is associated with energies of about 0.5 to about 350 Joules. The capacitance of the devices can range from about 25 to about 200 micro farads.[0118]
• In another embodiment, the S-ICD and US-ICD devices provide energy with a pulse width of approximately one millisecond to approximately 40 milliseconds. The devices can provide pacing current of approximately one milliamp to approximately 250 milliamps.[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]lead21 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]lead21 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 theproximal sense electrodes23 and25 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]incision31 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. Asubcutaneous pathway33 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 canister11 is then placed subcutaneously at the location of the incision or medially at the subcutaneous region at the left inframmary crease. Thesubcutaneous electrode13 is placed with a specially designed curved introducer set40 (see FIG. 8). The introducer set comprises acurved trocar42 and a stiff curved peel awaysheath44. 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 aproximal handle41 and acurved shaft43. Thedistal end45 of the trocar is tapered to allow for dissection of asubcutaneous path33 in the patient. Preferably, the trocar is cannulated having acentral Lumen46 and terminating in anopening48 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 awaysheath44 has aproximal pull tab49 for breaking the sheath into two halves along itsaxial shaft47. 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 thepull tab49 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 electrode27 and thesensing electrodes23 and25. Theinsulated lead21, 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 screwelectrode anchoring system52 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 electrodes13 and13′ of opposite polarity to the canister. The additionalsubcutaneous electrode13′ 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 twocoil electrodes27 and27′. Additionally, provided in the canister is means for selecting the optimum sensing arrangement between the foursense electrodes23,23′,25, and25′. The two electrodes are subcutaneously placed on the same side of the heart. As illustrated in FIG. 6, onesubcutaneous electrode13 is placed inferiorly and theother electrode13′ 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]canister11 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. In an embodiment, the canister is about 5 cm to about 40 cm long. 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 aninactive surface16 that is located on the exterior (convex) portion of the curvature. The leads of these embodiments, which are not illustrated except for theattachment port19 and the proximal end of thelead21, 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 electrodes26 and28 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 to18 depict particular US-ICD embodiments of 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. Thefirst end1413 is thicker than thesecond end1215. 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 electrodes1417 and1219 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 one embodiment, a 100 uF biphasic waveform is used of approximately 10-20 ms total duration and with the initial phase containing approximately ⅔ 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 electrodes1425 and1427. 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 insulatingareas1423. 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 5th rib 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.[0136]
• FIG. 16 schematically illustrates the method for implanting the US-ICD of the present invention. An[0137]incision1631 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 introducer1742 (see FIG. 17). The trocar has aproximal handle1641 and acurved shaft1643. The distal end1745 of the trocar is tapered to allow for dissection of a subcutaneous path in the patient. Preferably, the trocar is cannulated having acentral lumen1746 and terminating in an opening1748 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 end1413. The thick end is hollow inside allowing for the insertion of a coreoperational member1853. The core member comprises a housing1857 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 connectors1861 and1863 are electronically connected to the sense electrodes via pressure fit connectors (not illustrated) inside the thick end which are standard in the art. Plug connectors1865 and1867 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 anend cap1855, and a ribbed fitting1859 which creates a water-tight seal when the core member is inserted intoopening1851 of the thick end of the US-ICD.
• The S-ICD and US-ICD, in alternative embodiments, have the ability to detect and treat atrial rhythm disorders, including atrial fibrillation. The S-ICD and US-ICD have two or more electrodes that provide a far-field view of cardiac electrical activity that includes the ability to record the P-wave of the electrocardiogram as well as the QRS. One can detect the onset and offset of atrial fibrillation by referencing to the P-wave recorded during normal sinus rhythm and monitoring for its change in rate, morphology, amplitude and frequency content. For example, a well-defined P-wave that abruptly disappeared and was replaced by a low-amplitude, variable morphology signal would be a strong indication of the absence of sinus rhythm and the onset of atrial fibrillation. In an alternative embodiment of a detection algorithm, the ventricular detection rate could be monitored for stability of the R-R coupling interval. In the examination of the R-R interval sequence, atrial fibrillation can be recognized by providing a near constant irregularly irregular coupling interval on a beat-by-beat basis. A R-R interval plot during AF appears “cloudlike” in appearance when several hundred or thousands of R-R intervals are plotted over time when compared to sinus rhythm or other supraventricular arrhythmias. Moreover, a distinguishing feature compared to other rhythms that are irregularly irregular, is that the QRS morphology is similar on a beat-by-beat basis despite the irregularity in the R-R coupling interval. This is a distinguishing feature of atrial fibrillation compared to ventricular fibrillation where the QRS morphology varies on a beat-by-beat basis. In yet another embodiment, atrial fibrillation may be detected by seeking to compare the timing and amplitude relationship of the detected P-wave of the electrocardiogram to the detected QRS (R-wave) of the electrocardiogram. Normal sinus rhythm has a fixed relationship that can be placed into a template matching algorithm that can be used as a reference point should the relationship change.[0139]
• In other aspects of the atrial fibrillation detection process, one may include alternative electrodes that may be brought to bear in the S-ICD or US-ICD systems either by placing them in the detection algorithm circuitry through a programming maneuver or by manually adding such additional electrode systems to the S-ICD or US-ICD at the time of implant or at the time of follow-up evaluation. One may also use electrodes for the detection of atrial fibrillation that may or may not also be used for the detection of ventricular arrhythmias given the different anatomic locations of the atria and ventricles with respect to the S-ICD or US-ICD housing and surgical implant sites.[0140]
• Once atrial fibrillation is detected, the arrhythmia can be treated by delivery of a synchronized shock using energy levels up to the maximum output of the device therapy for terminating atrial fibrillation or for other supraventricular arrhythmias. The S-ICD or US-ICD electrode system can be used to treat both atrial and ventricular arrhythmias not only with shock therapy but also with pacing therapy. In a further embodiment of the treatment of atrial fibrillation or other atrial arrhythmias, one may be able to use different electrode systems than what is used to treat ventricular arrhythmias. Another embodiment, would be to allow for different types of therapies (amplitude, waveform, capacitance, etc.) for atrial arrhythmias compared to ventricular arrhythmias.[0141]
• 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.[0142]
• FIG. 14([0143]a) illustrates an embodiment of the subcutaneous lead electrode or “lead electrode assembly”100. Thelead electrode assembly100 is designed to provide anelectrode107 to be implanted subcutaneously in the posterior thorax of a patient for delivery of cardioversion/defibrillation energy. Thelead electrode assembly100 is further designed to provide a path for the cardioversion/defibrillation energy to reach theelectrode107 from the operational circuitry within thecanister11 of an S-ICD such as the embodiment shown in FIG. 1.
• The[0144]lead electrode assembly100 comprises a connector111, alead21, alead fastener146, anelectrode107 and anappendage118. The connector111 is connected to thelead21. Thelead21 is further connected to theelectrode107 with thelead fastener146. Theappendage118 is mounted to theelectrode107.
• The connector[0145]111 provides an electrical connection between the lead21 and the operational circuitry within thecanister11 of an S-ICD such as the embodiment shown in FIG. 1. Connector111 is designed to mate with theconnection port19 on thecanister11. In the embodiment under discussion, the connector111 meets the IS-1 standard.
• The[0146]lead21 of thelead electrode assembly100 provides an electrical connection between the connector111 and theelectrode107. Thelead21 comprises adistal end101 and aproximal end102. Thedistal end101 of thelead21 is attached to the connector111. Theproximal end102 of thelead21 is attached to electrode107 with thelead fastener146.
• The[0147]lead21 has a lead length, l_Lead, measured from the connector111 along thelead21 to thelead fastener146 of theelectrode107. The length of thelead21 is approximately 25 cm. In alternative embodiments, the lead lengths range between approximately 5 cm and approximately 55 cm.
• The[0148]lead fastener146 provides a robust physical and electrical connection between the lead21 and theelectrode107. Thelead fastener146 joins theproximal end102 of thelead21 toelectrode107.
• The[0149]electrode107 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 canister11.
• The[0150]electrode107 illustrated is generally flat and planar, comprising atop surface110, abottom surface115, adistal end103 and aproximal end104. Thelead fastener146 is attached to thetop surface110 of thedistal end103 of theelectrode107.
• The[0151]electrode107 may have shapes other than planar. In an alternate embodiment, theelectrode107 is shaped like a coil.
• The[0152]appendage118 is a member attached to theelectrode107 that can be gripped and used to precisely locate thelead electrode assembly100 during its surgical implantation within the patient.
• The[0153]appendage118 has a first end105, asecond end106, adistal edge121 and aproximal edge129. Thesecond end106 of theappendage118 is attached to thetop surface110 of theelectrode107. Theappendage118 is positioned such that itsproximal edge129 is within approximately 20 mm of theproximal end104 of theelectrode107. In alternate embodiments, theappendage118 is attached to theelectrode107 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[0154]appendages118.
• The appendage height, h[0155]_Appendage, is defined as the distance from the point of theappendage118 most distant from theelectrode107 to a point of theappendage118 closest to theelectrode107 measured along a line perpendicular to thetop surface110 of theelectrode107. The appendage height of theappendage118 illustrated, for example, would be measured between the first end105 of theappendage118 and thesecond end106 of theappendage118.
• The appendage height of the[0156]appendage118 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[0157]appendage118 that joins it to theelectrode107. The appendage interface of theappendage118 illustrated, for example, would be thesecond end106 of theappendage118.
• The appendage length, l[0158]_Appendage, is the length of theappendage118 along the appendage interface. The appendage interface of theappendage118 illustrated, for example, would be the length of thesecond end106 of theappendage118.
• The appendage length of the[0159]appendage118 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, theappendage118 is substantially as long as theelectrode107.
• More particularly, the[0160]appendage118 of the embodiment illustrated is afin120 comprising a fin core122 (phantom view) and acoating125.
• The[0161]fin core122 generally provides support for thefin120. Thefin core122 has afirst end126 and asecond end127. Thesecond end127 of thefin core122 is attached to thetop surface110 of theelectrode107.
• The[0162]fin core122 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, thefin core122 comprises any rugged material that can be attached to thefirst surface110 of theelectrode107.
• The[0163]coating125 is disposed around thefin core122. Thecoating125 provides a surface for thefin120 that can be easily gripped during the implantation of thelead electrode assembly100. Thecoating125 covering thefin core122 is composed of molded silicone. In an alternative embodiment, thecoating125 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[0164]fin120 is reinforced with a layer of Dacron® polymer mesh attached to the inside of thecoating125. 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 thecoating125. In another embodiment, thefin120 is reinforced with a layer of any polymeric material.
• FIG. 14([0165]b) illustrates a top view of thelead electrode assembly100. Theelectrode107 is substantially rectangular in shape, comprising a first pair ofsides108, a second pair ofsides109 and fourcorners112. In an alternative embodiment theelectrode107 has a shape other than rectangular. In this embodiment, thecorners112 of theelectrode107 are rounded. In an alternative embodiment thecorners112 of theelectrode107 are not rounded.
• The first pair of[0166]sides108 of theelectrode107 are substantially linear, substantially parallel to each other and are approximately 1 cm in length. The second pair ofsides109 of theelectrode107 are also substantially linear, substantially parallel with each other and are approximately 5 cm in length. Thebottom surface115 of theelectrode107 has an area of approximately 500 square mm. In alternative embodiments, the first pair ofsides108 and the second pair ofsides109 of theelectrode107 are neither linear nor parallel.
• In alternative embodiments, the length of the first pair of[0167]sides108 and second pair ofsides109 of theelectrode107 range independently between approximately 1 cm and approximately 5 cm. The surface area of thebottom surface115 of theelectrode107 ranges between approximately 100 sq. mm and approximately 2500 sq. mm. In one embodiment, the first pair ofsides108 and second pair ofsides109 of theelectrode107 are linear and have equal length, such that theelectrode107 is substantially square-shaped.
• The[0168]electrode107 comprises a sheet ofmetallic mesh114 further comprised of wovenwires119. Themetallic mesh114 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, themetallic mesh114 comprises any conductive material.
• In an alternate embodiment, the[0169]electrode107 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[0170]metallic mesh114 is approximately a 150 mesh, having approximately 150individual wires119 per inch. In alternative embodiments, themetallic mesh114 ranges between approximately a 50 mesh and approximately a 200 mesh. In this embodiment, the diameter of thewires119 of the mesh is approximately 1 mil. In alternative embodiments, the diameter of thewires119 ranges between approximately 1 and approximately 5 mils.
• The[0171]metallic mesh114 is first prepared by spot welding together thewires119 located along the first pair ofsides108 and second pair ofsides109 of themetallic mesh114. The excess lengths of wires are then ground or machined flush, so as to produce a smooth edge and to form asmooth border113. In an alternate embodiment, thewires119 located along the first pair ofsides108 and second pair ofsides109 of themetallic mesh114 are bent in toward themetallic mesh114 to form asmooth border113.
• The[0172]fin120 is attached to thetop surface110 of theelectrode107 in a position centered between the first pair ofsides108 of theelectrode107. In other embodiments, thefin120 is not centered between the first pair ofsides108 of theelectrode107.
• The[0173]fin120 is planar shape comprising afirst face191 and asecond face192. Thefirst face191 and thesecond face192 of thefin120 are substantially parallel to the first pair ofsides108 of theelectrode107. In other embodiments, thefirst face191 and thesecond face192 of thefin120 are positioned in orientations other than parallel to the first pair ofsides108 of theelectrode107.
• The[0174]first face191 and thesecond face192 of thefin120 extend from and substantially perpendicular to thetop surface110 of theelectrode107. In an alternative embodiment, thefirst face191 and thesecond face192 of thefin120 extend from thetop surface110 of theelectrode107 at other than right angles.
• The[0175]fin core122 of thefin120 is spot welded to themetallic mesh114 comprising theelectrode107. In another embodiment, thefin120 may be composed entirely of a polymeric material and attached to theelectrode107 by means known in the art.
• FIG. 14([0176]c) illustrates in detail a section of thelead21 of this embodiment. Thelead21 comprises an electrically insulatingsheath141 and anelectrical conductor142.
• The[0177]electrically insulating sheath141 is disposed around the electrical conductor142 (phantom view). The electrically insulatingsheath141 prevents the cardioversion/defibrillation energy passing through theelectrical conductor142 to the electrode from passing into objects surrounding thelead21. The electrically insulatingsheath141, comprises atube149 disposed around theelectrical conductor142. The tube is composed of either silicone, polyurethane or composite materials. One skilled in the art will recognize that thetube149 could alternately be composed of any insulating, flexible, bio-compatible material suitable to this purpose.
• In this embodiment, the[0178]electrical conductor142 comprises three highly-flexible, highly-conductive coiled fibers known as filars147 (phantom view). These fibers are wound in a helical shape through the electrically insulatingsheath141. In an alternate embodiment, the filars lie as linear cables within the electrically insulatingsheath141. In another alternate embodiment, a combination of helically coiled and linear filars lie within the electrically insulatingsheath141.
• FIG. 14([0179]d) illustrates a cross-section of a filar147. Thefilars147 of the embodiment illustrated comprise ametal core144, ametal tube143 and an insulatingcoating140. Themetal tube143 is disposed around themetal core144. The insulatingcoating140 is disposed around the metal tube. Themetal core144 is made of silver and themetal tube143 is made of MP35N® stainless steel, a product of SPS Technologies of Jenkintown, Pa. The insulatingcoating140 is made of teflon. Thefilars147 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[0180]filars147 further comprise an intermediate coating (not shown) disposed between themetal tube143 and the insulatingcoating140. This intermediate coating is made of platinum, iridium ruthenium, palladium or an alloy of these metals.
• In another alternative embodiment, the[0181]filars147 comprise DBS™ (drawn braised strands) also available from Fort Wayne Metals Research Products Corp. of Fort Wayne, Ind.
• Turning now to FIG. 14([0182]e), a cross section of thelead fastener146 is shown in detail. Thelead fastener146 provides a robust physical and electrical connection between the lead21 and theelectrode107.
• In this embodiment, the[0183]lead fastener146 comprises ametal strip157, a crimpingtube154 and a crimpingpin156. Themetal strip157 has afirst end150, asecond end151, and amiddle portion152. Thefirst end150 andsecond end151 of themetal strip157 are separated by themiddle portion152. Thefirst end150 andsecond end151 of themetal strip157 are attached to theelectrode107. In this embodiment, thefirst end150 andsecond end151 of thelead fastener146 are spot welded to thetop surface110 of themetallic mesh114 comprising theelectrode107. In other embodiments, other fastening methods known in the art can be used.
• The[0184]middle portion152 of themetal strip157 is raised away from theelectrode107 to permit the crimpingtube154 and electrically insulatingsheath141 of thelead21 to fit between themetal strip157 and theelectrode107.
• The[0185]middle portion152 of themetal strip157 contains acrimp point148. Thecrimp point148 squeezes the crimpingtube154 and electrically insulatingsheath141 of thelead21 thereby gripping it, and thereby providing a robust structural connection between the lead21 and theelectrode107.
• The[0186]filars147 of thelead21 are situated between the crimpingtube154 and crimpingpin156. The crimpingtube154 has a crimpingpoint155 which causes thefilars147 to be squeezed between crimpingtube154 and crimpingpin156. Agap159 in the electrically insulatingsheath141 allows the crimpingtube155 to make contact theelectrode107, thereby forming a robust electrical connection.
• The[0187]metal strip157, the crimpingtube154 and crimpingpin156 are each made of platinum iridium. In an alternative embodiment, themetal strip157, crimpingtube154 and crimpingpin156 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, themetal strip157, crimpingtube154 and crimpingpin156 are each made of any conductive material.
• FIG. 14([0188]f) illustrates an exploded view of thelead fastener146. In other embodiments, other types oflead fasteners146 known in the art are used.
• FIG. 15([0189]a) illustrates an alternative embodiment of thelead electrode assembly100. This embodiment is substantially similar to thelead electrode assembly100 illustrated in FIGS.14(a)-14(f). In this embodiment, however, theappendage118 lacks afin core122. Moreover, as seen in FIG. 15(a) thelead electrode assembly100 of this embodiment further comprises abacking layer130 andstitching139. Thebacking layer130 acts to insulate theelectrode107 so that cardioversion/defibrillation energy may not pass to the tissue of the patient that surrounds thetop surface110 of theelectrode107. This has the effect of focusing the cardioversion/defibrillation energy toward the heart of the patient through thebottom surface115 of theelectrode107.
• The[0190]backing layer130 comprises abase portion158 and anintegrated fin120. Thebase portion158 of thebacking layer130 comprises afirst surface131, asecond surface132, afirst side133 and asecond side134.
• The[0191]base portion158 of thebacking layer130 is attached to theelectrode107 such that thesecond surface132 of thebacking layer130 lies directly adjacent to thetop surface110 of theelectrode107.
• The[0192]base portion158 of thebacking layer130 is formed so that thefirst side133 and thesecond side134 are substantially parallel and of substantially the same size as the first pair ofsides108 of theelectrode107.
• FIG. 15([0193]b) illustrates a top view of thelead electrode assembly100 of this embodiment. Thebase portion158 of thebacking layer130 further comprises adistal end137 and aproximal end138.
• The[0194]distal end137 andproximal end138 of thebacking layer130 are parallel to and of substantially the same size as the second pair of sides109 (hidden) of theelectrode107. Thebacking layer130 contains anotch136 on itsdistal end137, through which thelead fastener146 rises.
• The[0195]base portion158 of thebacking layer130 is attached to theelectrode107 withstitching139. The stitching is composed of nylon. In alternate embodiments, the stitching is composed of any polymeric material.
• The[0196]backing layer130 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[0197]integrated fin120 of thebacking layer130 is formed from the same piece of material as thebacking layer130. Theintegrated fin120 has the same shape and dimensions as thefin120 of the embodiment in FIG. 14.
• In one embodiment, the[0198]integrated fin120 is reinforced with a layer of Dacron® polymer mesh attached to theintegrated fin120. In another embodiment, theintegrated fin120 is reinforced with a layer of any polymeric material.
• FIG. 16([0199]a) illustrates an alternative embodiment of thelead electrode assembly100. This embodiment is substantially similar to thelead electrode assembly100 illustrated in FIGS.14(a)-14(e). In this embodiment, however, thefin120 has a different construction.
• Here,[0200]fin120 comprises afirst fin section165, a second fin section160 andstitching168. Thefirst fin section165 is a rectangular sheet of polymeric material comprising aninside face167, anoutside face166, afirst side175 and asecond side174. Thefirst side175 andsecond side174 of thefirst fin section165 are substantially parallel and of substantially the same size.
• A line[0201]173 divides thefirst fin section165 into a first half171 and asecond half172. The line173 runs parallel to thefirst side175 of thefirst fin section165. The first half171 of thefirst fin section165 lies on one side of line173. Thesecond half172 of thefirst fin section165 lies on the other side of the line173.
• The second fin section[0202]160 is a rectangular sheet of polymeric material of the same size as thefirst fin section165 comprising aninside face162 and anoutside face161. The second fin section160 is divided in half substantially similarly to thefirst fin section165, thereby forming afirst half163 and asecond half164 of the second fin section160.
• In an alternate embodiment, the[0203]first fin section165 and second fin section are not rectangular in shape. In an alternate embodiment, thefirst fin section165 and second fin section have an oval shape.
• The first half[0204]171 of thefirst fin section165 is fastened to thefirst half163 of the second fin section160. Theinside face167 of the first half171 of thefirst fin section165 faces theinside face162 of thefirst half163 of the second fin section160. Thefirst fin section165 is fastened the second fin section160 withstitching168.
• The[0205]fin120 is attached to thetop surface110 of theelectrode107. To accomplish this, thesecond half172 of thefirst fin section165 is attached to thetop surface110 of theelectrode107 with thestitching169. Thesecond half164 of the second fin section160 is similarly attached to thetop surface110 of theelectrode107 with stitching (not shown).
• In one embodiment, the[0206]fin120 is reinforced with a layer of Dacron® polymer mesh positioned between thefirst fin section165 and the second fin section160 of theintegrated fin120. In another embodiment, the Dacron® polymer mesh is attached only to thefirst fin section165 or the second fin section160. In other embodiments, theintegrated fin120 is reinforced with a layer of any polymeric material attached to either or both fin sections.
• The appendage height of the[0207]fin120 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 thefin120 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 thefin120 is such that thefin120 is substantially as long as theelectrode107.
• FIG. 17([0208]a) illustrates a side plan view of an alternative embodiment of thelead electrode assembly100. Thelead electrode assembly100 comprises a connector111, alead21, alead fastener146, anelectrode107, abacking layer130 with anintegrated fin tab180, a moldedcover220 and anappendage118.
• The connector[0209]111 is connected to thelead21. Thelead21 is further connected to theelectrode107 with thelead fastener146. Thebacking layer130 is positioned over theelectrode107. Thefin tab180 protrudes from thebacking layer130. The moldedcover220 is disposed around thelead fastener146 and thebacking layer130. The moldedcover220 is further disposed around thefin tab180 of thebacking layer118 to form theappendage118. The moldedcover220 also partially envelops theelectrode107.
• The connector[0210]111 and thelead21 are substantially similar to the connector111 and thelead21 described with reference to FIGS.14(a)-14(f). The lead comprises adistal end101 and aproximal end102. Thedistal end101 of thelead21 is attached to the connector111. Theproximal end102 of thelead21 is connected to theelectrode107 by thelead fastener146.
• In this embodiment, the[0211]lead fastener146 comprises a first crimpingtube200, a crimpingpin202 and a second crimpingtube201. The first crimpingtube200 connects theproximal end102 of thelead21 to the crimpingpin202. The second crimpingtube201 connects the crimpingpin202 to theelectrode107.
• The[0212]electrode107 comprises a distal end103 (phantom view), aproximal end104, atop surface110 and abottom surface115. The electrode further comprises three sections: amain body217, amandrel219 and amandrel neck218.
• The[0213]main body217 of theelectrode107 is the region of theelectrode107 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 sides108 (not shown) and a second pair ofsides109. The first pair ofsides108 of theelectrode107 are substantially parallel to each other. The second pair ofsides109 of theelectrode107 are also substantially parallel to each other. In another embodiment, the first pair ofsides108 and the second pair ofsides109 of theelectrode107 are nonparallel. Themain body217 of theelectrode107 is positioned under thebacking layer130, so that thetop surface110 of the electrode faces thebacking layer130.
• The[0214]mandrel219 is a region of theelectrode107 shaped to facilitate the connection of theelectrode107 to thelead21 via thelead fastener146. The mandrel of the electrode is crimped onto to the crimpingpin202 of thelead fastener146 with the second crimpingtube201, so that a robust physical and electrical connection is formed. Themain body217 of theelectrode107 is connected to themandrel219 of theelectrode107 via themandrel neck218 of theelectrode107.
• The[0215]backing layer130 comprises abase portion158 and anintegrated fin tab180. Thebase portion158 of thebacking layer130 comprises afirst surface131, asecond surface132, adistal end137 and aproximal end138.
• The[0216]base portion158 of thebacking layer130 is positioned such that itssecond surface132 is adjacent to thetop surface110 of theelectrode107. Thebase portion158 of thebacking layer130 is sized and positioned so that thedistal end137 andproximal end138 of thebase portion158 of thebacking layer130 overlay the second pair ofsides109 of themain body217 of theelectrode107. Thedistal end137 andproximal end138 of the are also substantially parallel and of substantially the same size as the second pair ofsides109 of theelectrode107.
• The integrated[0217]fin tab180 of thebacking layer130 is formed from the same piece of material as thebase portion158 of thebacking layer130. Theintegrated fin tab180 is formed on thefirst surface131 of thebase portion158 of thebacking layer130.
• The integrated[0218]fin tab180 comprises aproximal edge183, adistal edge184, a top185 and a bottom186. Thebottom186 of theintegrated fin tab180 is joined to thefirst surface131 of thebase portion158 of thebacking layer130. Theproximal edge183 and thedistal edge184 of theintegrated fin tab180 extend from, and substantially perpendicular to thefirst surface131 of thebase portion158 of thebacking layer130. Theproximal edge183 anddistal edge184 of theintegrated fin tab180 are parallel with each other. Theintegrated fin tab180 is positioned so that itsproximal edge183 is substantially flush with theproximal end138 of thebase portion158 of thebacking layer130.
• The[0219]backing layer130 is composed of polyurethane. In an alternative embodiment, thebacking layer130 is composed of silicone. In another alternative embodiment, thebacking layer130 is composed of any polymeric material.
• The molded[0220]cover220 envelops and holds together the components of thelead electrode assembly100. The moldedcover220 also provides rigidity to thelead electrode assembly100. The moldedcover220 envelops thelead fastener146 and thebacking layer130. Thefin120 is formed when the moldedcover220 covers thefin tab180. The thickness of the resultingfin120 is approximately 2 mm. In alternate embodiments, the thickness of thefin120 is between approximately 1 mm and approximately 3 mm.
• The appendage height of the[0221]fin120 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 thefin120 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 thefin120 is such that the fin is as long as the backing layer. In one embodiment, the appendage length of thefin120 is such that the fin is as long as theelectrode107. In one embodiment, the appendage length of thefin120 is such that the fin is as long as the moldedcover220.
• The molded[0222]cover220 also partially covers thebottom surface115 of theelectrode107. In this way, the moldedcover220 attaches thebacking layer130 to theelectrode107.
• The molded[0223]cover220 in this embodiment is made of silicone. In an alternate embodiment, the moldedcover220 is made of any polymeric material.Stitching360 holds the moldedcover220, theelectrode107 and thebacking layer130 together.
• In one embodiment, the[0224]fin120 is reinforced with a layer of Dacron® polymer mesh positioned between the moldedcover220 and theintegrated fin tab180. In another embodiment, the Dacron® polymer mesh is attached only to the moldedcover220. In other embodiments, thefin120 is similarly reinforced with a layer of any polymeric material.
• As shown in FIG. 17([0225]b), thefin120 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 thefin120 during the insertion of thelead electrode assembly100 into the patient. The slope-shapedfin120 is constructed so that theproximal edge183 anddistal edge184 of theintegrated fin tab180 are not parallel with each other. Instead,proximal edge183 of theintegrated fin tab180 can be curved so that theproximal edge183 of theintegrated fin tab180 is closer to theproximal edge184 at the top185 of theintegrated fin tab180, than at the bottom186 of theintegrated fin tab180. In alternate embodiments, theproximal edge183 of theintegrated fin tab180 is not curved. Instead, theproximal edge183 of theintegrated fin tab180 is straight, and forms an acute angle with thefirst surface131 of thebacking layer130. In one alternate embodiment, theproximal edge183 of theintegrated fin tab180 forms a 45 degree angle with thefirst surface131 of thebacking layer130. In alternate embodiments, thedistal edge184 of theintegrated fin tab180 is curved. In alternate embodiments, thedistal edge184 of theintegrated fin tab180 is straight and shaped so that it forms an acute angle with thefirst surface131 of thebacking layer130.
• FIG. 17([0226]c) illustrates a front plan view of thelead electrode assembly100 seen in FIG. 17(a). Thebase portion158 of thebacking layer130 further comprises afirst side133 andsecond side134. Thefirst side133 andsecond side134 of thebase portion158 of thebacking layer130 are substantially parallel. In an alternate embodiment, thefirst side133 andsecond side134 of thebacking layer130 are not parallel. Thebase portion158 of thebacking layer130 is sized so that it is substantially the same size and shape as themain body217 of theelectrode107.
• The integrated[0227]fin tab180 of thebacking layer130 is planar, comprising afirst face181 and asecond face182. Thefirst face181 andsecond face182 of thefin tab180 are substantially parallel with each other and with thefirst side133 andsecond side134 of thebacking layer130. Thefirst face181 andsecond face182 of thefin tab180 extend from, and substantially perpendicular to thefirst surface131 of thebacking layer130. In another embodiment, thefirst face181 andsecond face182 of thefin tab180 extend from thefirst surface131 of thebacking layer130 at angles other than a right angle.
• In an alternate embodiment, the[0228]first face181 and asecond face182 of theintegrated fin tab180 of thebacking layer130 are not substantially parallel to each other. Instead, they are angled, such that they are closer together at the top185 than they are at the bottom186 of theintegrated fin tab180. This shape can reduce the resistance offered by the tissue of the patient as it slides against thefin120 during the insertion of thelead electrode assembly100 into the patient.
• In another embodiment, the[0229]first face181 and asecond face182 of theintegrated fin tab180 of thebacking layer130 are angled, such that they are further apart at the top185 than they are at the bottom186 of theintegrated fin tab180. This shape can make thefin120 easier to grip with a tool, such as a hemostat.
• The[0230]fin tab180 extends from thebacking layer130 at a position centered between thefirst side133 and thesecond side134 of thebacking layer130. In an alternate embodiment, thefin tab180 is not centered between thefirst side133 and thesecond side134 of thebacking layer130.
• An[0231]eyelet301 is formed in thefin120 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 ahole225 through the moldedcover220 and between thefaces181 and182 offin tab180. In an alternate embodiment, no eyelet is formed in thefin120.
• The[0232]bottom surface115 of theelectrode107 comprises aperiphery213 and acenter211. The moldedcover220 forms askirt222 around theperiphery213 of thebottom surface115 of theelectrode107. Theskirt222 of the moldedcover220 covers theperiphery213 of thebottom surface115 of theelectrode107.
• The[0233]skirt222 of the moldedcover220 can act to focus cardioversion/defibrillation energy emitted from theelectrode107 of thelead electrode assembly100 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 theactive surface15 of the canister11 (seen in FIG. 1) without passing through the patient's heart. Theskirt222 of thelead electrode assembly100 acts to minimize the loss of cardioversion/defibrillation energy to surrounding body tissues, or from being diverted away from the patient's heart.
• The[0234]center211 of thebottom surface115 of theelectrode107 is not covered by the moldedcover220 and is left exposed. The width of theperiphery213 of thebottom surface115 of theelectrode107 covered by the moldedcover220 is approximately 0.125 cm.
• The area of the exposed[0235]center211 of thebottom surface115 of theelectrode107 is approximately 500 square mm. In alternative embodiments, the length of the first pair ofsides108 and the second pair ofsides109 of theelectrode107 vary, such that the area of thecenter211 of thebottom surface115 of the electrode has a surface area between approximately 100 sq. mm. and approximately 2500 sq. mm.
• FIG. 17([0236]d) illustrates an exploded top view of thelead fastener146 of the embodiments illustrated in FIGS.17(a)-17(c). The lead fastener connects theproximal end102 of thelead21 and thedistal end103 of theelectrode107.
• In this embodiment, the[0237]lead fastener146 comprises a first crimpingtube200, a crimpingpin202 and a second crimpingtube201. The crimpingpin202 comprises a first side203 and asecond side204.
• The crimping[0238]tube200 crimps thefilars147 of the lead21 (here, only onerepresentative filar147 is shown) to the first side203 of crimpingpin202. Themandrel219 of theelectrode107 is then wrapped around thesecond side204 of the crimpingpin202. Crimpingtube201 crimps themandrel219 to thesecond side204 of the crimpingpin202.
• The first crimping[0239]tube200, the second crimpingtube201 and the crimpingpin202 are each made of platinum iridium. In an alternative embodiment, the first crimpingtube200, the second crimpingtube201 and the crimpingpin202 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 crimpingtube200, the second crimpingtube201 and the crimpingpin202 each comprise any conductive material.
• The[0240]electrode107 in this embodiment comprises a sheet ofmetallic mesh206 prepared by the process described with reference to FIG. 14. Theelectrode107 has a width measured parallel to the second pair ofsides109 of theelectrode107. The width of themandrel neck218 of theelectrode107 is approximately 3 mm wide. The width of the mandrel of theelectrode107 is approximately 5 mm wide.
• The first pair of[0241]sides108 of theelectrode107 are approximately 5 cm in length. The second pair ofsides109 of theelectrode107 are approximately 1.9 cm in length. In alternative embodiments, the length of the first pair ofsides108 and the second pair ofsides109 of theelectrode107 range independently from approximately 1 cm to approximately 5 cm.
• The[0242]electrode107 of this embodiment further comprises fourcorners112. Thecorners112 of theelectrode107 are rounded. In an alternate embodiment, thecorners112 of theelectrode107 are not rounded.
• FIGS.[0243]17(e)-17(g) illustrate the size and position of thefin120 on the molded cover of thelead electrode assembly100.
• FIGS.[0244]18(a)-18(c) illustrate an alternative embodiment of thelead electrode assembly100. This embodiment is substantially similar to the embodiments illustrated in FIGS.17(a)-17(g). In this embodiment, however, the appendage height of thefin120 is approximately 1 cm. The appendage length of thefin120 in this embodiment is approximately 3.5 cm.
• As shown in FIG. 18([0245]a),stitching302 is placed through the moldedcover220 and thefin120 to prevent the moldedcover220 from sliding off thefin tab180 when the moldedcover220 is subjected to a force directed away from theelectrode107.
• As shown in FIG. 18([0246]c), the fin120 (phantom view) extends approximately two thirds of the length of theelectrode107.
• FIG. 19 illustrates an alternative embodiment of the[0247]lead electrode assembly100. This embodiment is substantially similar to the embodiments illustrated in FIGS.17(a)-17(g). In this embodiment, however, the backing layer130 (not shown) inside the moldedcover220 is curved. This results in anelectrode107 that has a curvature of radius r, such that thebottom surface115 of theelectrode107 is concave.
• Because a[0248]curved electrode107 may more closely approximate the curvature of the patient's ribs, this curvature may have the effect of making thelead electrode assembly100 more comfortable for the patient. In one embodiment, the radius r of the curvature varies throughout theelectrode107 such that it is intentionally shaped to approximate the shape of the ribs.Lead electrode assemblies100 can be custom manufactured with anelectrode107 with a curvature r that matches the curvature of the intended patient's ribcage in the vicinity of the ribcage adjacent to which theelectrode107 is to be positioned.
• In an alternative embodiment,[0249]lead electrode assemblies100 are manufactured with anelectrode107 with a radius r that matches the curvature of the ribcage of a statistically significant number of people.
• In another embodiment,[0250]lead electrode assemblies100 withelectrodes107 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[0251]electrode107 of thelead electrode assembly100 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.[0252]20(a)-20(c) illustrate an alternative embodiment of thelead electrode assembly100. This embodiment is substantially similar to the embodiments illustrated in FIGS.17(a)-17(g). In this embodiment, however, thebacking layer130 lacks anintegrated fin tab180 mounted on thefirst surface131 of thebacking layer130. Moreover, this embodiment further comprises abacking layer400 having afin tab405.
• FIGS.[0253]20(a) and20(b) illustrate only thebacking layer400, thefin tab405 and theelectrode107 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([0254]a) illustrates a top plan view of thebacking layer400 and theelectrode107. Thebacking layer400 is positioned over theelectrode107. Theelectrode107 of this embodiment is substantially similar to theelectrode107 of the embodiment illustrated in FIG. 17(d). In the complete embodiment, themandrel219 of theelectrode107 is joined to the lead21 (not shown) by a lead fastener146 (not shown) as shown in FIG. 17(a).
• The[0255]backing layer400 is a flat, planar member comprising adistal end137 and aproximal end138. Thebacking layer400 further comprises afirst side133, asecond side134, afirst surface131, and a second surface132 (not shown). Thebacking layer400 further comprises a width, W, measured as the distance between thefirst side133 and thesecond side134.
• The[0256]backing layer400 includes afin tab405 that is formed from the same piece of material as thebacking layer400. Thefirst side133 of thebacking layer400 lies over one of the first pair ofsides108 of theelectrode107 except over afin tab region407. In thefin tab region407, thebacking layer400 is wider than theelectrode107. In thefin tab region407, thefirst side133 forms afin tab405 that protrudes from part of thefirst side133 of thebacking layer400 outside thefin tab region407. Thefin tab405 extends from thefirst side133 of thebacking layer400 in an orientation substantially parallel to thetop surface110 of theelectrode107, beyond the first side108 (phantom view) of theelectrode107.
• The[0257]fin tab405 comprises afirst face410 and a second face411 (not shown). Thefirst face410 of thefin tab405 is an extension of thefirst surface131 of thebacking layer400. The second face411 of thefin tab405 is an extension of thesecond surface132 of thebacking layer400.
• Aside from the[0258]fin tab405, thebacking layer405 is formed so that it is of substantially the same size and shape as themain body217 of theelectrode107.
• The[0259]backing layer400, including thefin tab405, is composed of polyurethane. In an alternate embodiments thebacking layer400 andfin tab405 are composed of any polymeric material.
• FIG. 20([0260]b) is a side plan view of thebacking layer400 and theelectrode107. Thebacking layer400 is positioned over theelectrode107 such that thesecond surface132 of thebacking layer400 is placed adjacent to thetop surface110 of theelectrode107.
• FIG. 20([0261]c) illustrates a bottom plan view of the complete embodiment, in which the backing layer400 (not shown), the lead fastener146 (not shown) and the fin tab405 (phantom view) are coated with a moldedcover220. When the moldedcover220 is applied over thebacking layer400, afin424 is formed over the fin tab405 (phantom view). Thefin424 comprises aproximal end404 and adistal end403.
• In one embodiment, the[0262]fin424 is reinforced with a layer of Dacron® polymer mesh positioned between the moldedcover220 and thefin tab405. In another embodiment, the Dacron® polymer mesh is attached only to the moldedcover220. In other embodiments, thefin424 is similarly reinforced with a layer of any polymeric material.
• The appendage height, h[0263]_Appendage, of thefin424 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 thefin424 of this embodiment is measured between theproximal end404 and thedistal end403 of thefin424. L_Appendageis measured where thefin424 joins the rest of thelead electrode assembly100. 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 thefin424 is such that thefin424 runs the length of theelectrode107. In one embodiment, the appendage length of thefin424 is such that thefin424 runs the length of the backing layer130 (not shown). In one embodiment, the appendage length of thefin424 is such that thefin424 runs the length of the moldedcover220.
• FIG. 20([0264]d) illustrates a bottom plan view of an alternate embodiment of thelead electrode assembly100. This embodiment is substantially similar to thelead electrode assembly100 illustrated in FIGS.20(a)-20(c). In this embodiment, however,proximal end404 of thefin424 is sloped. The slope shape of thefin424 is formed by the shape of the fin tab405 (phantom view) inside thefin424. Thebacking layer400 gradually widens in the fin tab region407 (not shown) with distance from the proximal end138 (not shown) to the distal end137 (not shown) of the backing layer130 (not shown) until the appendage height is reached. Theproximal end404 of thefin424 is straight and forms an acute angle with thefirst side133 of thebase portion158 of the backing layer130 (not shown). In an alternate embodiment, theproximal end404 of thefin424 forms a 45 degree angle with thefirst side133 of thebase portion158 of the backing layer130 (not shown). In another embodiment, theproximal end404 of thefin424 is curved slope.
• In alternate embodiments, the[0265]distal end403 of thefin424 is straight and shaped so that it forms an acute angle with thefirst side133 of thebase portion158 of the backing layer130 (not shown). In alternate embodiments, thedistal end403 of thefin424 is curved.
• FIGS.[0266]21(a)-21(c) illustrate an alternative embodiment of thelead electrode assembly100. This embodiment is substantially similar to the embodiment illustrated in FIGS.15(a)-15(b). Theintegrated fin120 is absent, however, from thebacking layer130.
• The[0267]lead electrode assembly100 of this embodiment further comprises acylindrical rod500 having aloop515 formed therein. Theloop515 comprises theappendage118 of this embodiment. Theloop515 is a member attached to theelectrode107 that can be gripped and used to precisely locate theelectrode107 during its surgical implantation within the patient.
• FIG. 21([0268]a) illustrates a side plan view of the embodiment. Thecylindrical rod500 comprises a firststraight portion510, a secondstraight portion512 and a portion formed into aloop515. The firststraight portion510 is separated from the secondstraight portion512 by theloop515.
• The[0269]rod500 is made of platinum iridium. In an alternative embodiment, therod500 is made of titanium or platinum.
• The first[0270]straight portion510 and secondstraight portion512 are spot welded to thetop surface110 of theelectrode107. Theloop515 in therod500 extends away from thetop surface110 of theelectrode107.
• The[0271]backing layer130 is similar to thebacking layer130 illustrated in FIGS.15(a)-15(b). Thebacking layer130 is disposed over theelectrode107. The firststraight portion510 and secondstraight portion512 of therod500 are positioned between thesecond surface132 of thebacking layer130 and thetop surface110 of theelectrode107.
• FIG. 21([0272]b) illustrates a cross-sectional rear plan view of the embodiment of the lead electrode assembly shown in FIG. 21(a). The firststraight portion510 and secondstraight portion512 are positioned such that they are parallel to the first pair ofsides108 of theelectrode107. The firststraight portion510 and secondstraight portion512 are both centered between the first pair ofsides108 of theelectrode107. In an alternative embodiment, the firststraight portion510 and secondstraight portion512 are not parallel to and centered between the first pair ofsides108 of theelectrode107.
• FIG. 21([0273]c) illustrates a top plan view of the embodiment of the lead electrode assembly shown in FIG. 21(a). Anaperture517 is formed in thebacking layer130. Theaperture517 in the backing layer is positioned such that theloop515 extends through and beyond theaperture517 in a direction away from thetop surface110 of theelectrode107. Thebacking layer130 is attached to theelectrode107 withstitching139.
• FIGS.[0274]22(a)-22(d) illustrate an alternative embodiment of thelead electrode assembly100. This embodiment is substantially similar to the embodiment illustrated in FIGS.15(a)-15(b). This embodiment comprises abacking layer610, however, that lacks theintegrated fin120 illustrated in FIGS.15(a)-15(b).
• FIG. 22([0275]a) illustrates a top plan view of thebacking layer610 of this embodiment prior to its attachment to the rest of thelead electrode assembly100. Thebacking layer610 is cut in a pattern as shown. The backing layer comprises afirst surface131, a second surface132 (not shown), adistal end137, aproximal end138, afirst side133, asecond side134 and an indented fin-formingregion620. The indented fin-formingregion620 comprises afirst edge690 and asecond edge691.
• The[0276]backing layer610 is formed so that thefirst side133 and thesecond side134 are substantially parallel and of substantially the same size as the first pair ofsides108 of theelectrode107. Theproximal end138 is formed so that it is substantially perpendicular to thefirst side133 and thesecond side134 of thebacking layer610. Theproximal end138 is longer than the second pair ofsides109 of theelectrode107 by a length A. Thebacking layer610 has a varying width C measured from itsdistal end137 to itsproximal end138 along a line parallel to itsfirst side133.
• The backing layer is divided into three sections. A[0277]first backing section693, asecond backing section692 and an indented fin-formingregion620 of length A. The length of the fin-formingregion620, A, is approximately 10 mm. In other embodiments, the length of the fin-formingregion620, A, ranges between approximately 2 mm and approximately 20 mm.
• The area within the indented fin-forming[0278]region620 is equally divided into afirst fin area612 and asecond fin area615. Thedividing line617 between thefirst fin area612 and thesecond fin area615 is substantially parallel to thefirst side133.
• The width, C, of the[0279]backing layer610 is equal to the distance between the second pair ofsides109 of theelectrode107 except in the indented fin-formingregion620. In the indented fin-formingregion620, the width, C, of thebacking layer610 is B. The width, B, of thebacking layer610 in the fin-formingregion620, is approximately 1 cm. In alternate embodiments, the width, B, of thebacking layer610 in the fin-formingregion620 ranges between approximately 2 mm and approximately 6 cm. In other embodiments, however, the fin-formingregion620 ranges between 2 mm and the width, C, of thebacking layer610. In other embodiments, the fin-formingregion620 is longer than the width, C, of thebacking layer610.
• The variation in width between the areas inside and outside the indented fin-forming[0280]region620, forms thefirst edge690 and asecond edge691 of the fin-formingregion620.
• A first notch[0281]136(a) is formed on thedistal end137 thefirst edge690 of the fin-formingregion620 of thebacking layer130. A second notch136(b) is formed on thedistal end137 thesecond edge691 of the fin-formingregion620 of thebacking layer130.
• The[0282]backing layer610 in this embodiment is formed of flexible silicone. In alternative embodiments thebacking layer610 is formed of any bio-compatible, flexible polymeric material.
• FIG. 22([0283]b) illustrates a top plan view of thelead electrode assembly100 of this embodiment. Thebacking layer610 is attached to theelectrode107, so that thefirst edge690 and asecond edge691 of the fin-formingregion620 of thebacking layer610 meet. This causes thebacking layer610 in thefirst fin area612 and thesecond fin area615 to fold together to form afin120.
• The first notch[0284]136(a) and second notch136(b) formed on thedistal end137 thefirst edge690 andsecond edge691 of the fin-formingregion620 of thebacking layer130 meet to form anotch136 on thedistal end137 of the backing layer, through which thelead fastener146 rises.Stitching660 holds the backing layer to theelectrode107.
• FIG. 22([0285]c) illustrates a side plan view of thelead electrode assembly100 of this embodiment.Stitching660 holds thefirst fin area612 and asecond fin area615 of thebacking layer610 together to form thefin120.
• FIG. 22([0286]d) illustrates a front plan view of thelead electrode assembly100 of this embodiment. In one embodiment, thefin120 is reinforced with a layer of Dacron® polymer mesh positioned between thefirst fin area612 and asecond fin area615. In another embodiment, the Dacron® polymer mesh is attached only to eitherfirst fin area612 or thesecond fin area615. In other embodiments, thefin120 is similarly reinforced with a layer of any polymeric material.
• FIGS.[0287]22(e) and22(f) illustrate an alternative embodiment of thelead electrode assembly100. This embodiment is substantially similar to the embodiment illustrated in FIGS.22(a)-22(d). Thebacking layer610 is substantially similar to thebacking layer610 illustrated in FIG. 22(a). Thebacking layer610 in this embodiment, however, is cut alongline617. Thefin120 of this embodiment comprises aproximal edge129. Theproximal edge129 of thefin120 is slope-shaped. The sloped shape can reduce the resistance offered by the tissue of the patient as it slides against thefin120 during the insertion of thelead electrode assembly100 into the patient.
• FIGS.[0288]23(a) and23(b) illustrate a property of the embodiment of thelead electrode assembly100 illustrated in FIGS.22(e) and22(f). Thebacking layer610 is flexible, such that the substantiallyplanar fin120 formed therefrom is flexible and able to fold. Because the ability of thefin120 to fold effectively reduces its appendage height, it may make the fin more comfortable to the patient after it is implanted.
• FIG. 23([0289]a) showsfin120 in an upright condition. When pressure is applied perpendicular to thefirst surface131 of backing layer in thefirst fin area612, alongline677 for example, thefin120 folds as shown in FIG. 23(b). When thefin120 folds, its appendage height, H_Appendage, is reduced. This can be seen by a comparison between FIG. 23(a) and FIG. 23(b).
• The[0290]backing layer610 in this embodiment is formed of a polymeric material. In an alternative embodiment, thebacking layer610 is formed of any bio-compatible, flexible polymeric material.
• FIGS.[0291]24(a)-24(c) illustrate an alternative embodiment of thelead electrode assembly100. This embodiment is substantially similar to the embodiment illustrated in FIGS.22(a)-22(d).
• As shown in FIG. 24([0292]a), however, the material from thefirst fin area612 and thesecond fin area615 of thebacking layer610 is not fastened together with stitching660 in this embodiment. The resultingappendage118 is formed in the shape of a tube.
• In alternate embodiments, the[0293]backing layer610 is coupled to theelectrode107 such that the material from thefirst fin area612 and thesecond fin area615 of thebacking layer610 does not touch except at thedividing line617 between thefirst fin area612 and thesecond fin area615. The separation between thefirst fin area612 and thesecond fin area615 of thebacking layer610 can allow theappendage118 of this embodiment to be highly flexible. This flexibility can reduce the resistance offered by the tissue of the patient as it slides against theappendage118 during the insertion of thelead electrode assembly100 into the patient.
• FIG. 24([0294]b) illustrates a side plan view of the embodiment illustrated in FIG. 24(a). Theappendage118 of this embodiment comprises aproximal edge129. Theproximal edge129 of theappendage118 is slope-shaped. The sloped shape can reduce the resistance offered by the tissue of the patient as it slides against theappendage118 during the insertion of thelead electrode assembly100 into the patient.
• In alternate embodiments, the[0295]proximal edge129 of the tube formed by theappendage118 is closed. In one embodiment, theproximal edge129 of theappendage118 is closed by a cap (not shown). In another embodiment, theproximal edge129 of theappendage118 is closed with stitching placed between thefirst fin area612 and thesecond fin area615 only at theproximal edge129 of theappendage118. In another embodiment, theproximal edge129 of theappendage118 is closed by any other means known in the art for this purpose.
• FIG. 24([0296]b) illustrates a top plan view of the embodiment illustrated in FIGS.24(a)-24(b).
• FIGS.[0297]25(a)-25(d) illustrate an alternative embodiment of thelead electrode assembly100. This embodiment is substantially similar to the embodiment illustrated in FIGS.15(a)-15(b). Thebacking layer130 of this embodiment, however, lacks anintegrated fin120.
• FIG. 25([0298]a) illustrates a front plan view of the lead electrode assembly. Thefin120 in this embodiment comprises afin head700 and flexible joiningmaterial702.
• The[0299]fin head700 comprises a rectangular sheet having afirst face705, asecond face706, afirst end710 and asecond end712. Thefin head700 further comprises a height measured along thefirst face705 between thefirst end710 and thesecond end712 and a length measured perpendicular to its height.
• The[0300]fin head700 is made of rigid silicone, which has a high durometer. In alternate embodiments, thefin head700 is composed of any rigid bio-compatible material, such as a rigid bio-compatible polymeric material.
• The flexible joining[0301]material702 comprises a rectangular sheet having afirst face720, asecond face721, afirst end718 and asecond end719. The flexible joiningmaterial702 further comprises a height measured along the first face between thefirst end718 and thesecond end719. The flexible joiningmaterial702 also comprises a length measured perpendicular to its height. The length of the flexible joiningmaterial702 is the same as the length offin head700.
• The[0302]second end712 of thesecond face706 of thefin head700 is attached to thefirst end718 of thefirst face720 of the flexible joiningmaterial702. Thefin head700 is attached to the flexible joiningmaterial702 withstitching725. Thesecond end719 of thefirst face720 of the flexible joiningmaterial702 is attached to thefirst surface131 of thebacking material130. The flexible joiningmaterial702 is attached to thebacking material130 withstitching730.
• The flexible joining[0303]material702 is made of flexible silicone. It will be recognized by one skilled in the art, however, that the flexible joiningmaterial702 may be made from many other flexible materials, such as a flexible polymeric material.
• FIG. 25([0304]b) illustrates a property of thefin120. When pressure is applied perpendicular to thefirst surface705 of the fin head205, thefin120 folds as shown. When thefin120 folds, its appendage height, H_Appendage, is reduced. This can be seen by a comparison between FIG. 25(a), which shows thefin120 in an upright position and FIG. 25(b) that shows thefin120 in a folded position.
• FIG. 25([0305]c) illustrates a top planar view of thelead electrode assembly100 of the embodiment illustrated in FIGS.25(a) and25(b). Neither the corners of theelectrode107 nor thecorners735 of thebacking layer130 of this embodiment are rounded. In an alternate embodiment, both the corners of theelectrode107 and thecorners735 of thebacking layer130 of this embodiment are rounded.
• FIG. 26 illustrates an alternative embodiment of the[0306]lead electrode assembly100. This embodiment is substantially similar to the embodiment illustrated in FIGS.25(a)-25(d). Thebacking layer130 of this embodiment, however, lacks afin head700 and flexible joiningmaterial702.
• Moreover, the[0307]appendage118 in this embodiment comprises atube740 having an interior755, anexterior756, aproximal end757 and adistal end758. The tube comprises a sheet ofmaterial750. The sheet ofmaterial750 is substantially rectangular having a first pair ofsides751, a second pair ofsides752, afirst surface753 and asecond surface754.
• The sheet of[0308]material750 is folded so that its first pair ofsides751 abut each other. The folded sheet ofmaterial750 forms atube740. Thefirst surface753 of the sheet ofmaterial750 faces theinterior755 of thetube740. Thesecond surface754 of the sheet ofmaterial750 faces the exterior of thetube756. In folding the sheet ofmaterial750 so that the first pair ofsides751 abut each other, the second pair ofsides752 of the sheet ofmaterial750 are folded in a circular shape to form theproximal end757 anddistal end758 of thetube740. This results in thetube740 having a cylindrical shape. The diameter of the circularproximal end757 anddistal end758 of thetube756 is approximately 5 mm. In alternate embodiments, the diameter range between approximately 1 mm and approximately 10 mm. The length of thetube756 as measured between theproximal end757 anddistal end758 of thetube756 is approximately 1 cm. In alternate embodiments, length of thetube756 ranges between approximately 2 mm and approximately 6 cm. In one embodiment, thetube756 is substantially as long as theelectrode107.
• The[0309]second surface754 of the sheet ofmaterial750 is attached to thefirst surface131 of thebacking layer130. The first pair ofsides751 of the sheet ofmaterial750 are attached to thebacking layer130 withstitching760.
• In alternate embodiments, the[0310]proximal end757 of thetube740 is closed. In one embodiment, theproximal end757 of thetube740 is closed by a cap (not shown). In another embodiment, theproximal end757 of thetube740 is closed by holding one of the second pair ofsides752 of the sheet ofmaterial750 closed with stitching. In another embodiment, theproximal end757 of thetube740 is closed by any other means known in the art for this purpose.
• It should be noted that the[0311]appendage118 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.
• FIG. 27 illustrates an alternative embodiment of the[0312]lead electrode assembly100. This embodiment is substantially similar to the embodiment illustrated in FIG. 26. Thetube740 comprising a sheet ofmaterial750, however, is absent from this embodiment.
• Moreover, the[0313]appendage118 of this embodiment comprises atube770 having an interior755 an exterior756, aproximal end757 and adistal end758. The tube comprises a first sheet ofmaterial775, a second sheet ofmaterial776 and a third sheet ofmaterial777. The first sheet ofmaterial775, the second sheet ofmaterial776 and the third sheet ofmaterial777 are all substantially rectangular in shape. Each comprises a first pair ofsides784, a second pair ofsides786, afirst surface788 and asecond surface789. The first pair ofsides784 of each sheet of material are parallel to each other. In another embodiment, the first pair ofsides784 of each sheet of material are non-parallel. The second pair ofsides786 of each sheet of material are parallel to each other. In another embodiment, the second pair ofsides786 of each sheet of material are non-parallel.
• The first pairs of[0314]sides784 of each sheet of material are attached to the first pair ofsides784 of the other sheets of material. In this way the second pair ofsides786 of the first sheet ofmaterial775, the second sheet ofmaterial776 and the third sheet ofmaterial777 form a triangular shapedproximal end757 anddistal end758 of thetube770. The sheets of material are attached to each other such that thesecond surface789 of each sheet of material faces theinterior755 of thetube770. The sheets of material are attached to each other withstitching791.
• The height of the[0315]tube770 is approximately 5 mm. In alternate embodiments, the height ranges between approximately 1 mm and approximately 10 mm. The length of thetube770 as measured between theproximal end757 anddistal end758 of thetube770 is approximately 1 cm. In alternate embodiments, length of thetube770 ranges between approximately 2 mm and approximately 6 cm. In one embodiment, thetube770 is substantially as long as theelectrode107.
• The second sheet of[0316]material776 is attached to thebacking layer130 withstitching790. Thefirst surface788 of the second sheet ofmaterial776 is positioned next to thefirst surface131 of thebacking layer130.
• 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[0317]first surface788 of each sheet of material. In another embodiment, the Dacron® polymer mesh is attached to thesecond surface789 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[0318]proximal end757 of thetube770 is closed. In one embodiment, theproximal end757 of thetube770 is closed by a cap. In another embodiment, theproximal end757 of thetube770 is closed by holding thesides786 of the first sheet ofmaterial775, the second sheet ofmaterial776 and the third sheet ofmaterial777 that form theproximal end757 of thetube770 together with stitching. In another embodiment, theproximal end757 of thetube770 is closed by any other means known in the art for this purpose.
• FIGS.[0319]28(a)-28(d) illustrate various possible positions for theappendage118 relative to thelead21 of thelead electrode assembly100. Additionally, up to this point, all embodiments of theelectrode107 illustrated and discussed have had a rectangular shape. These figures illustrate alternative embodiments withelectrodes107 of different shapes.
• At this point, it is useful to set out two definitions in order to discuss the possible orientation of[0320]appendages118.
• The interface line is defined as the center line of the[0321]appendage118 as traced on theelectrode107. FIG. 28(a) illustrates theinterface line800 of theappendage118 of alead electrode assembly100.
• The line of the lead is defined as the line along which the[0322]lead21 of thelead electrode assembly100 enters thelead fastener146. The line of thelead805 ofline21 is shown as it enters the lead fastener146 (in phantom). As the lead21 approaches thelead fastener146, theclosest section807 of the lead21 forms the line of the lead. When thelead21 is not bent, theentire lead21 lies along the line of the lead.
• FIG. 28([0323]b) illustrates an embodiment wherein thelead21 is not bent and theentire lead21 lies along the line of thelead805.
• The electrode length, L[0324]_Electrode, is the length of theelectrode107 as measured along theinterface line800.
• In the embodiments of the[0325]lead electrode assembly100 shown in FIGS.28(b) and28(c), theinterface line800 is the same line as the line of thelead805. In the embodiment shown in FIG. 28(a) theinterface line800 is parallel with the line of thelead805.
• In the embodiment of the[0326]lead electrode assembly100 shown in FIG. 28(d), theinterface line800 intersects the lead fastener146 (phantom view).
• FIGS.[0327]28(e)-28(h) show various additional electrode shapes disposed in variouslead electrode assemblies100. The electrode shapes are not limited, however, to the shapes specifically illustrated.
• The[0328]electrode204 depicted in FIG. 28(e) has a “thumbnail” shape. Theproximal end104 of thiselectrode107 is generally rounded. As theelectrode107 moves distally along its length, the conductive surface terminates at thedistal end103 of theelectrode107.
• An ellipsoidal shaped[0329]electrode107 is depicted in FIG. 28(f). Theproximal end104 of the ellipsoidal shapedelectrode107 is generally rounded. As the ellipsoidal shapedelectrode107 moves distally along its length, the conductive surface terminates in a roundeddistal end103.
• A circular shaped[0330]electrode107 is illustrated in FIG. 28(g).
• A triangular shaped[0331]electrode107 is depicted in FIG. 28(h). Triangular shapedelectrodes107 also incorporate electrodes that are substantially triangular in shape. In particular to FIG. 28(h), the corners of the triangularshaped electrode107 are rounded.
• Several lead electrode[0332]assembly manipulation tools927 have been developed to manipulate the lead electrode assemblies during their surgical implantation.
• FIG. 29 illustrates an embodiment of a lead electrode[0333]assembly manipulation tool927. The lead electrodeassembly manipulation tool927 comprises anenhanced hemostat930 used to manipulatelead electrode assemblies100 comprising an eyelet during their implantation in patients.
• The enhanced[0334]hemostat930 comprises the following components: a hemostat having afirst prong931, asecond prong932, ahinge939 and aneyelet pin940. Thefirst prong931 is attached to thesecond prong932 by thehinge939. The eyelet pin is attached to thesecond prong932.
• The[0335]first prong931 comprises afirst end933 and asecond end934. Thesecond prong932 comprises afirst end935 and asecond end936. 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[0336]first prong931 is pivotally attached to thesecond prong932 by thehinge939. The hinge is attached to thefirst prong931 approximately 10 cm from thefirst end933. In this embodiment, the hinge is attached to thesecond prong932 approximately 10 cm from thesecond end935.
• The[0337]eyelet pin940 can be inserted through theeyelet301 of afin120 of thelead electrode assembly100 such as thelead electrode assembly100 discussed with reference to FIGS.17(a)-17(g) as a means of capturing thelead electrode assembly100 prior to its implantation in a patient.
• The[0338]eyelet pin940 is a cylindrical member having afirst end941 and asecond end942. In an alternate embodiment, theeyelet pin940 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 theeyelet pin940 is approximately 8 mm. In alternate embodiments, the length of theeyelet pin940 ranges from approximately 4 to approximately 15 mm.
• The first end of the[0339]eyelet pin940 is attached to thesecond prong932, approximately 8 mm from thesecond end936 of thesecond prong932. In alternate embodiments, theeyelet pin940 is attached to thesecond prong932 at various lengths from thesecond end936 of thesecond prong932.
• The[0340]eyelet pin940 is attached to thesecond prong932 in an orientation perpendicular to the length of thesecond prong932. Theeyelet pin940 is attached to thesecond prong932 so that it extends away from thesecond end934 of thefirst prong931.
• 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.[0341]
• We now turn to a discussion of the positions of the components that comprise an entire S-ICD system including the[0342]lead electrode assembly100 when it is implanted in a patient.
• FIGS.[0343]30(a) and30(b) illustrate an embodiment of the S-ICD system implanted in a patient as a means of providing cardioversion/defibrillation energy.
• FIG. 30([0344]a) is a perspective view of a patient's ribcage with an implanted S-ICD system. The S-ICD canister11 is implanted subcutaneously in the anterior thorax outside theribcage1031 of the patient, left of thesternum920 in the area over thefifth rib1038 andsixth rib1036. The S-ICD canister11, however, may alternately be implanted anywhere over the area between the third rib and the twelfth rib. Thelead21 of thelead electrode assembly100 is physically connected to the S-ICD canister11 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[0345]lead21 of thelead electrode assembly100 travels from the S-ICD canister11 to theelectrode107, which is implanted subcutaneously in the posterior thorax outside theribcage1031 of the patient in the area over theeighth rib1030 andninth rib1034. Theelectrode107, may alternately be implanted subcutaneously anywhere in the posterior thorax outside theribcage1031 of the patient in the area over thethird rib1030 and thetwelfth rib1034. Thebottom surface115 of theelectrode107 faces the ribcage. The electrode or active surface15 (phantom view) of thecanister11 also faces the ribcage.
• FIG. 30([0346]b) is a cross-sectional side plan view of the patient's rib cage. Here it is seen that thelead21 travels around the circumference of the thorax, in the subcutaneous layer beneath the fat1050 between the outside of theribcage1031 and theskin1055 covering the thorax.
• We now turn to a discussion of a method by which the[0347]lead electrode assembly100 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[0348]incision905 is made in the patient900 in the anterior thorax between the patient's third and fifth rib, left of thesternum920. 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([0349]a) shows a bottom view cross-section of the patient900, along the line32(a) shown in FIG. 31. Ahemostat930, withprongs932 is introduced into theincision905. Thehemostat930 is inserted with its prongs together without anything gripped between them. Theprongs932 of thehemostat930 are pushed through the fat1050 between theskin1055 of the thorax and theribcage1031 to create asubcutaneous path1090. Theprongs932 of thehemostat930 can alternately be pushed beneath the fat1050 that lies between theskin1055 of the thorax and theribcage1031 to create asubcutaneous path1090 between the fat1050 and theribcage1031.
• The hemostat is moved around the[0350]ribcage1031 until thesubcutaneous path1090 reaches within approximately 10 cm of thespine1035 between theeighth rib1030 and ninth rib1034 (this location is best seen in FIG. 30(a)) between theskin1055 and theribcage1031. Thesubcutaneous path1090 can alternately be made to reach any location between theskin1055 and theribcage1031 between the patient's third and twelfth rib. Thehemostat930 is then withdrawn. Alternately, thehemostat930 can be moved around theribcage1031 until thesubcutaneous path1090 terminates at atermination point1085 at which aline1084 drawn from thetermination point1085 to theincision905 would intersect theheart910.
• Next, as shown in FIG. 32([0351]b), theappendage118 of alead electrode assembly100, is squeezed between thetongs932 of ahemostat930.
• As shown in FIG. 32([0352]c), thelead electrode assembly100 andhemostat tongs932 are introduced to thesubcutaneous path1090 and pushed through the subcutaneous path until thelead electrode assembly100 reaches thetermination point1085 of the path. Theappendage118 of thelead electrode assembly100 is then released from thetongs932 of thehemostat930. Thehemostat930 is then withdrawn from thesubcutaneous path1090.
• In an alternative method, the[0353]enhanced hemostat930 seen in FIG. 29 is used to introduce thelead electrode assembly100 into thesubcutaneous path1090 created as discussed above. After thesubcutaneous path1090 is created, thelead electrode assembly100 is attached to theenhanced hemostat930 as shown in FIG. 32(d). Eyelet pin1108 is inserted through theeyelet301 in thefin120 of thelead electrode assembly100. Theenhanced hemostat930 is then used to introduce thelead electrode assembly100 into thesubcutaneous path1090, as shown in FIG. 32(c). Thelead electrode assembly100 is then moved through thesubcutaneous path1090 until theelectrode107 reaches the end of thepath1085. Theenhanced hemostat930 is then moved until thelead electrode assembly100 is released from theeyelet pin940. Theenhanced hemostat930 is then withdrawn from thesubcutaneous path1090.
• FIGS.[0354]33(a)-33(c) illustrate an alternative embodiment of thelead electrode assembly100. This embodiment is substantially similar to the embodiments illustrated in FIGS.17(a)-17(g). Thebacking layer130 of this embodiment, however, lacks anintegrated fin tab180. Moreover, theappendage118 of thelead electrode assembly100 of this embodiment comprises arail1100.
• FIG. 33([0355]a) illustrates therail1100 of thelead electrode assembly100 of this embodiment. Therail1100 is a member attached to theelectrode107 that can be captured by a lead electrode assembly manipulation tool and used to precisely locate theelectrode107 during its surgical implantation within the patient. Therail1100 comprises three sections: afoundation1105, ariser1110 and a head1115. Thefoundation1105 is separated from the head1115 by theriser1125.
• The[0356]foundation1105 comprises a flat, substantially planar member, comprising a first pair ofsides1106 and a second pair ofsides1107. The first pair ofsides1106 of thefoundation1105 are substantially linear and substantially parallel. In an alternate embodiment, the first pair ofsides1106 of thefoundation1105 are neither linear nor parallel. The length of the first pair ofsides1106 of thefoundation1105 is approximately 2 cm. In alternate embodiments, the length of the first pair ofsides1106 of thefoundation1105 ranges from approximately 2 mm to approximately 6 cm. In an alternate embodiment, the first pair ofsides1106 of thefoundation1105 are as long as the electrode107 (not shown) of the lead electrode assembly100 (not shown).
• The second pair of[0357]sides1107 of thefoundation1105 are substantially linear and substantially parallel. In an alternate embodiment, the second pair ofsides1107 of thefoundation1105 are neither linear nor parallel. The length of the second pair ofsides1107 of thefoundation1105 is approximately 1 cm. In alternate embodiments, the length of the second pair ofsides1107 of thefoundation1105 ranges from approximately 0.5 cm to approximately 3 cm.
• The[0358]foundation1105 further comprises atop surface1120 and abottom surface1121. Thefoundation1105 has a thickness, measured as the distance between thetop surface1120 and thebottom surface1121. The thickness of thefoundation1105 is 2 mm. In alternate embodiments, the thickness of thefoundation1105 ranges between approximately 1 mm and approximately 5 mm.
• Turning now to the[0359]riser1110, theriser1110 comprises a flat, substantially planar protrusion from thetop surface1120 of thefoundation1105 of therail1100. The riser comprises afirst face1125, asecond face1126, a top1127, a bottom1128, aproximal end1123 and adistal end1124. Thefirst face1125 andsecond face1126 are parallel to each other and perpendicular to thetop surface1120 of thefoundation1105. Thefirst face1125 and asecond face1126 of theriser1110 are parallel to the first pair ofsides1106 of thefoundation1105. Thebottom1128 of theriser1110 joins thefoundation1105 in a position centered between the first pair ofsides1106 of thefoundation1105. Theproximal end1123 of theriser1110 and thedistal end1124 of theriser1110 are parallel to each other and perpendicular to thetop surface1120 of thefoundation1105. In other embodiments, theproximal end1123 of theriser1110 and thedistal end1124 of theriser1110 are not parallel to each other.
• In one embodiment, the[0360]proximal end1123 of theriser1110 is not perpendicular thetop surface1120 of thefoundation1105. Instead, theproximal end1123 of theriser1110 is sloped, so that theproximal end1123 and thedistal end1124 of theriser1110 are closer at the top1127 of theriser1110 than at thebottom1128 of the riser. A slantedproximal end1123 make therail1100 of thelead electrode assembly100 offer less resistance against the tissues of the patient during insertion into the patient.
• The height of the riser, H[0361]_Riser, is measured as the distance between thetop surface1120 of thefoundation1105 to the head1115, perpendicular to thetop surface1120 of thefoundation1105. 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[0362]riser1110 has a width, measured as the distance between thefirst face1125 and thesecond face1126. The width of theriser1110 is 2 mm. In alternate embodiments, the width of theriser1110 ranges from approximately 1 mm to approximately 6 mm.
• Turning now to the head[0363]1115, the head1115 is a flat, substantially planar member. The head1115 comprises a first pair ofsides1136, a second pair ofsides1137, atop surface1116 and a bottom surface1117 (not shown). The first pair ofsides1136 and the second pair ofsides1137 of the head1115 are substantially linear and substantially parallel. In an alternate embodiment, the first pair ofsides1136 of the head1115 are neither linear nor parallel. In an alternate embodiment, the second pair ofsides1137 of the head1115 are neither linear nor parallel.
• The length of the first pair of[0364]sides1136 of the head1115 is equal to the length of the first pair ofsides1106 of thefoundation1105. In alternate embodiments, the length of the first pair ofsides1136 of the head1115 is unequal to the length of the first pair ofsides1106 of thefoundation1105. The length of the second pair ofsides1137 of the head1115 is approximately 5 mm. In alternate embodiments, the length of the second pair ofsides1137 of the head1115 ranges from approximately 3 mm to approximately 10 mm.
• The[0365]bottom surface1117 of the head1115 joins the top1127 of theriser1110 opposite thefoundation1105 of therail1100. Thetop surface1116 and thebottom surface1117 of the head1115 are parallel to thetop surface1120 of thefoundation1105. In an alternate embodiment, thetop surface1116 and thebottom surface1117 of the head1115 are not parallel to thetop surface1120 of thefoundation1105.
• The head[0366]1115 has a thickness, measured as the distance between thetop surface1116 and thebottom surface1117 of the head1115. The thickness of the head1115 is approximately 2 mm. In alternate embodiments, the thickness of the head ranges between approximately 2 mm and approximately 10 mm.
• The[0367]foundation1105, the head1115 and theriser1110 are made of stainless steel. In alternate embodiments, some or all of the sections of therail1100 are made of metals other than stainless steel. In alternate embodiments, some or all of the sections of therail1100 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[0368]foundation1105, the head1115 and theriser1110 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([0369]b), the position of therail1100 within thelead electrode assembly100 will be discussed. Therail1100 is positioned so that itsbottom surface1121 is adjacent to and covers a region of thefirst surface131 of thebacking layer130. The rail is centered between thefirst side133 andsecond side134 of thebacking layer130. In an alternate embodiment, the rail is not centered between thefirst side133 andsecond side134 of thebacking layer130.
• In an alternate embodiment, there is no[0370]backing layer130 and therail1100 is positioned so that itsbottom surface1121 is adjacent to thetop surface110 of theelectrode107.
• Turning now to the[0371]electrode107 of this embodiment, theelectrode107 is the same shape and size as theelectrode107 discussed with reference to FIGS.17(a)-(g). In alternative embodiments, the length of the first pair of sides108 (not shown) and second pair of sides109 (not shown) of theelectrode107 range independently between approximately 1 cm and approximately 5 cm.
• Turning now to the molded[0372]cover220, theskirt222 of the moldedcover220 partially covers thebottom surface115 of theelectrode107 as discussed with reference to FIG. 17(d). The moldedcover220 further substantially covers thefirst surface131 of thebacking layer130. The moldedcover220 does not cover thefirst surface131 of thebacking layer220 in the region in which thebottom surface1121 of therail1100 is adjacent to thebacking layer130. Instead, the moldedcover220 in this region substantially covers thetop surface1120 of therail1100. The moldedcover220 abuts thefirst face1125 andsecond face1126 of theriser1110 of therail1100.
• Turning to FIG. 33([0373]c), the position of thelead21 and theappendage118 will now be discussed. Theinterface line800 of theappendage118 and the line of thelead805 are the same line. In an alternate embodiment,interface line800 of theappendage118 and the line of thelead805 are not the same line. The line of thelead805 is centered between the first pair of sides108 (phantom view) of the electrode107 (phantom view). In an alternate embodiment, the line of thelead805 is not centered between the first pair ofsides108 of theelectrode107.
• FIG. 34 illustrates an alternative embodiment of the[0374]lead electrode assembly100. This embodiment is substantially similar to the embodiment illustrated in FIGS.33(a)-33(c). In this embodiment, however, the dimensions of theelectrode107 are different from those of the embodiment illustrated in FIGS.33(a)-33(c).
• The first pair of[0375]sides108 of the electrode107 (phantom view) are approximately 2.4 cm in length. The second pair ofsides109 of theelectrode107 are approximately 4 cm in length. In alternative embodiments, the length of the first pair ofsides108 and second pair ofsides109 of theelectrode107 range independently between approximately 1 cm and approximately 5 cm.
• The[0376]interface line800 of therail1100 is parallel to the line of thelead805. In an alternate embodiment, theinterface line800 of therail1110 is not parallel to the line of thelead805. Theinterface line800 of therail1100 is centered between the first pair ofsides108 of theelectrode107. In an alternate embodiment, theinterface line800 of therail1100 is not centered between the first pair ofsides108 of theelectrode107.
• The line of the[0377]lead805 is not centered between the first pair ofsides108 of theelectrode107. Because thelead805 is not centered between the first pair ofsides108 of theelectrode107, thelead rail1110 may be more easily accessed by a lead electrode manipulation tool (not shown). In an alternate embodiment, the line of thelead805 is centered between the first pair ofsides108 of theelectrode107.
• FIG. 35 illustrates a lead electrode[0378]assembly manipulation tool927 useful for manipulating a lead electrode assembly (not shown) having anappendage118 comprising arail1100 during the implantation of thelead electrode assembly100 in a patient. Examples of suchlead electrode assembly100 embodiments are shown in FIGS.33(a)-33(c) and34.
• The lead electrode[0379]assembly manipulation tool927 comprises ahandle1142, arod1144 and arail fork1146. Thehandle1142 is connected to therod1144. Therail fork1146 is also connected to therod1144.
• The[0380]rod1144 is a cylindrical member with a diameter of approximately 4 mm, approximately 25 cm in length, having aproximal end1147 and adistal end1148. Therod1144 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.[0381]
• The[0382]handle1142 is a cylindrical member with a diameter sized to fit comfortably in the palm of a surgeon's hand. The rod is connected to theproximal end1147 of therod1144. In an alternate embodiment, thehandle1142 is not cylindrical. In an alternate embodiment, thehandle1142 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.[0383]
• Turning now to FIG. 35([0384]b), therail fork1146 is attached to thedistal end1148 of therod1144. The rod further comprises aslot1162 in its distal end. The rail fork comprises a pair oftines1151 separated by agap1153 and atine base1160 having atang1161.
• Each of the pair of[0385]tines1151 has aproximal end1154 and a distal end1155. The proximal ends1154 of the pair oftines1151 are attached to thetine base1160. Each of the pair oftines1151 has a substantially rectangular form with straight inner sides1156 and straightouter sides1157. The distal ends1155 of each of the pair oftines1151 are rounded. The length of the pair oftines1151, measured from the distal end1155 to theproximal end1154, is substantially equal to the length of the first pair ofsides1106 of therail1100 of thelead electrode assembly100. In alternate embodiments, the length of the pair oftines1151 is substantially greater than or less than the length of the first pair ofsides1106 of therail1100.
• The pair of[0386]tines1151 are separated by agap1153 formed by the inner sides1156 of the pair oftines1151 and thetine base1160.
• The pair of[0387]tines1151 and thetine base1160 comprising therail fork1146 are punched from a single sheet of steel having a thickness of approximately 3 mm. In other embodiments, therail fork1146 is composed of titanium, a polymeric material or any other material suitable for this purpose. In one embodiment, thehandle1142, therod1144 and therail fork1146 are all made from the same piece of material.
• FIG. 35([0388]c) illustrates a side plan view of the lead electrodeassembly manipulation tool927. Therod1144 further comprises aslot1162 in itsdistal end1148. Thetine base1160 connects the pair oftines1151 to thedistal end1148 of therod1144. Thetine base1160 comprises a tang1161 (phantom view). Thetang1161 is inserted in theslot1162 in therod1144. Thetang1161 is welded in theslot1162 of therod1144.
• We now turn to a description of the use of the lead electrode[0389]assembly manipulation tool927 in the implantation of alead electrode assembly100 into a patient.
• As discussed with reference to FIG. 31, an[0390]incision905 is made in the patient900. As discussed with reference to FIG. 32(a), asubcutaneous path1090 is created in the patent900 with ahemostat932.
• As shown in FIG. 35([0391]d), thelead electrode assembly100 is then captured by the lead electrodeassembly manipulation tool927. Therail1110 of thelead electrode assembly100 is inserted into therail fork1146 of the lead electrodeassembly manipulation tool927. The riser1110 (phantom view) of the rail is placed into thegap1153 between the pair oftines1151 of therail fork1146. The pair oftines1151 fit between thebottom surface1117 of the head1115 of therail1100 and the moldedcover220. Therail1100 is slid toward the proximal end1155 of the pair oftines1151 until theriser1110 of therail1100 reaches thetine base1160 of therail fork1146. Thelead21 of thelead electrode assembly100 can then be pulled in toward thehandle1142 of the lead electrodeassembly manipulation tool927 until it is taught. This acts to prevent therail1100 of thelead electrode assembly100 from sliding toward thedistal end1151 of the pair oftines1151 of therail fork1146.
• As discussed with reference to FIG. 32([0392]c), the lead electrodeassembly manipulation tool927 may then be used to place thelead electrode assembly100 into theincision905 of the patient900 and used to move theelectrode107 to thetermination point1085 of thesubcutaneous path1090.
• The[0393]lead electrode assembly100 is then released from the lead electrodeassembly manipulation tool927. To achieve this, thelead21 of thelead electrode assembly100 is released so that the pair oftines1151 of therail fork1146 of the lead electrodeassembly manipulation tool927 can slide relative to therail1100 of thelead electrode assembly100. The lead electrodeassembly manipulation tool927 may then be extracted from thesubcutaneous path1090, leaving thelead electrode assembly100 behind.
• FIGS.[0394]36(a)-36(b) illustrate an alternative embodiment of thelead electrode assembly100. This embodiment is substantially similar to the embodiments illustrated in FIGS.17(a)-17(g). Thebacking layer130 of this embodiment, however, lacks anintegrated fin tab180. Moreover, thelead electrode assembly100 of this embodiment further comprises apocket1300.
• FIG. 36([0395]a) illustrates a cross-sectional side plan view of this embodiment. Thepocket1300 comprises a layer ofmaterial1315 andstitching360. The pocket further comprises an interior1305 and anopening1310. The layer ofmaterial1315 is attached to the moldedcover220 with thestitching360. The moldedcover220 is, in turn, attached to theelectrode107.
• The molded[0396]cover220 comprises anouter surface1330 and atop surface1331. Theouter surface1330 of the moldedcover220 is the surface of the moldedcover220 that does not lie adjacent to thebacking layer131 or theelectrode107. Thetop surface1331 of the moldedcover220 faces away from, and parallel to theelectrode107.
• The layer of[0397]material1315 of thepocket1300 comprises an inner face1316 and anouter face1317. The layer ofmaterial1315 is attached to thetop surface1331 of the moldedcover220 so that the inner face1316 of the layer ofmaterial1315 faces thetop surface1331 of the moldedcover220. The inner face1316 of the layer ofmaterial1315 also faces thetop surface110 of theelectrode107.
• The layer of[0398]material1315 is made of polyurethane. In other embodiments, the layer ofmaterial1315 is made of any bio-compatible material suitable for this purpose. In other embodiments, the layer ofmaterial1315 is made of any biocompatible polymeric material.
• The[0399]stitching360 fastening the layer ofmaterial1315 to thetop surface1331 of the moldedcover220 is comprised of nylon. In alternate embodiments, thestitching360 comprises any polymeric material.
• FIG. 36([0400]b) illustrates a top plan view of thelead electrode assembly100 of FIG. 36(a). Thetop surface1331 of the moldedcover220 has afirst side1333, asecond side1334, adistal end1336, aproximal end1337, a length and a width.
• The[0401]distal end1336,proximal end1337,first side1333 andsecond side1334 of thetop surface1331 of the moldedcover220 are positioned substantially over the distal end137 (phantom view), proximal end138 (phantom view), first side133 (not shown) and second side134 (not shown) of the backing layer130 (phantom view) respectively.
• The width of the[0402]top surface1331 of the moldedcover220 is measured as the distance between thefirst side1333 andsecond side1334 of the back surface. The length of thetop surface1331 of the molded cover is measured as the distance between thedistal end1336 andproximal end1337 of the moldedcover220.
• The layer of[0403]material1315 comprises aperiphery1318 and amiddle portion1319. More particularly, the layer ofmaterial1315 comprises adistal end1320, aproximal end1321, afirst side1322 and asecond side1323. Theperiphery1318 of the layer ofmaterial1315 comprises thedistal end1320, theproximal end1321, thefirst side1322 and thesecond side1323 of the layer ofmaterial1315. Themiddle portion1319 of the layer ofmaterial1315 comprises the area between thedistal end1320, theproximal end1321, thefirst side1322 and thesecond side1323 of the layer ofmaterial1315.
• The[0404]pocket1300 formed by the layer ofmaterial1315 further comprises abounded region1325 and acenter1326. Thebounded region1325 of thepocket1300 is attached to theback face1317 of the moldedcover220. Thecenter1326 of thepocket1300 is not attached to theback face1317 of the moldedcover220. Stitching360 in thebounded region1325 is used to attach the layer ofmaterial1315 to the moldedcover220.
• In the embodiment under discussion, the[0405]bounded region1325 of thepocket1300 comprises a portion of theperiphery1318 of the layer ofmaterial1315. Thebounded region1325 of thepocket1300 comprises theproximal end1321, thefirst side1322 and thesecond side1323 of the layer ofmaterial1315. In this embodiment, thebounded region1325 of thepocket1300 does not comprise thedistal end1320 of the layer ofmaterial1315. Thecenter1326 of thepocket1300 comprises themiddle portion1319 of the layer ofmaterial1315. Thebounded region1325 is curved around thecenter1326 of thepocket1300 in a “U” shape. Thebounded region1325 of thepocket1300 does not completely enclose thecenter1326 of thepocket1300.
• In this embodiment, the[0406]bounded region1325 of the pocket comprises a contiguous portion of theperiphery1318 of the layer ofmaterial1315. In an alternate embodiment, thebounded region1325 of the pocket comprises a plurality of segmented portions of theperiphery1318 of the layer ofmaterial1315.
• In an alternate embodiment the[0407]bounded region1325 of thepocket1300 does not comprise any portion of theperiphery1318 of the layer ofmaterial1315. In alternate embodiments, thebounded region1325 comprises any shape that could be traced on the layer ofmaterial1315 that partially encloses acenter1326. In one embodiment, thebounded region1325 of thepocket1300 is a portion of a circle's circumference (not shown) that does not touch theperiphery1318 of the layer ofmaterial1315. Thecenter1326 is the area inside the circle.
• In an alternate embodiment, the[0408]pocket1300 comprises a sheet of molded silicone. The molded silicone is fused to the moldedcover220 in thebounded region1325.
• The[0409]opening1310 of thepocket1300 comprises the area between thedistal end1320 of the layer ofmaterial1315 and thetop surface1331 of the moldedcover220. Theinterior1305 of thepocket1300 comprises the area between themiddle portion1319 of the layer ofmaterial1315 and thetop surface1331 of the moldedcover220.
• The layer of[0410]material1315 is positioned so that itsfirst side1322 andsecond side1323 are positioned over thefirst side1333 andsecond side1334 of thetop surface1331 of the moldedcover220 respectively. The layer ofmaterial1315 is positioned so that itsproximal end1321 is positioned over theproximal end1337 of thetop surface1331 of the moldedcover220.
• The layer of[0411]material1315 is sized so that its length is shorter than the length of thetop surface1331 of the moldedcover220. In alternate embodiments, the layer ofmaterial1315 is sized so that its length is equal to, or longer than the length of thetop surface1331 of the moldedcover220.
• The[0412]proximal end1321 of the layer ofmaterial1315 is sized so that its width is substantially equal to the width of theproximal end1337 of thetop surface1331 of the moldedcover220. The layer ofmaterial1315 is sized so that its width steadily increases toward itsdistal end1320.
• The[0413]first side1318 of thedistal end1320 of the layer ofmaterial1315 is fastened to thefirst side1333 of thetop surface1331 of the moldedcover220. Thesecond side1323 of thedistal end1320 of the layer ofmaterial1315 is fastened to thesecond side1334 of thetop surface1331 of the moldedcover220.
• Since the[0414]first end1322 of the layer ofmaterial1315 is wider than thetop surface1331 of the moldedcover220, the layer ofmaterial1315 separates from thetop surface1331 of the moldedcover220 to form theinterior1305 of thepocket1300.
• In an alternate embodiment, the[0415]lead electrode assembly100 lacks a moldedcover220 and thepocket1300 is attached directly to thebacking layer130. In another alternate embodiment thelead electrode assembly100 lacks a moldedcover220 and abacking layer130 and thepocket1300 is attached directly to theelectrode107. In a further alternate embodiment, thepocket1300 is molded as part of the moldedcover220.
• FIG. 36([0416]c) illustrates a cross-sectional side plan view of an alternative embodiment of thelead electrode assembly100. This embodiment is substantially similar to the embodiment illustrated in FIGS.36(a)-36(b). Thebacking layer130 of this embodiment, however, further comprises afin120 positioned in theinterior1305 of thepocket1300. Thefin120 of this embodiment is substantially similar to thefin120 of the embodiment illustrated in FIG. 17(b).
• The[0417]fin120 comprises anintegrated fin tab180 formed on thebacking layer130. The moldedcover220 covers theintegrated fin tab180 to form thefin120. Theintegrated fin tab180 has a slope-shapedproximal edge183. The sloped-shape of the resultingfin120 permits a thefin120 to fit deeply into theinterior1305 of thepocket1300. The hood can act to reduce the resistance presented by the tissues of the patient against thefin120 and any tool used to grasp thefin120 during insertion of thelead electrode assembly100. Such a hood can be placed over any fin discussed in the specification to perform this function or any other function.
• In alternate embodiments, appendages other than a fin are positioned between the[0418]pocket1300 and theelectrode107, in theinterior1305 of thepocket1300. In one embodiment, a loop such as that discussed with reference to FIGS.21(a)-21(c) is positioned in theinterior1305 of thepocket1300. In another embodiment, a tube such as that discussed with reference to FIG. 26 is positioned in theinterior1305 of thepocket1300.
• FIGS.[0419]37(a) and37(b) illustrates an alternate embodiment of thelead electrode assembly100. This embodiment is substantially similar to the embodiment illustrated in FIGS.36(a)-36(b).
• FIG. 37([0420]a) illustrates a bottom plan view of thelead electrode assembly100 of this embodiment. In this embodiment, theelectrode107 is thumbnail shaped.
• FIG. 37([0421]b) illustrates a top plan view of thelead electrode assembly100 of this embodiment. Thetop surface1331 of the moldedcover220 is shaped to accommodate the thumbnail shapedelectrode107.
• Like the embodiment discussed with reference to FIGS.[0422]36(a) and36(b), thepocket1300 comprises a layer ofmaterial1315. In this embodiment, however, the layer ofmaterial1315 has a roughly triangular shape. The layer ofmaterial1315 comprises aperiphery1318 and amiddle portion1319. More particularly, the layer of material comprises afirst side1340, asecond side1341 and athird side1342 of the layer ofmaterial1315. Theperiphery1318 of the layer of material comprises thefirst side1340, thesecond side1341 and thethird side1342 of the layer ofmaterial1315. Themiddle portion1319 of the layer ofmaterial1315 comprises the area between thefirst side1340, thesecond side1341 and thethird side1342 of the layer ofmaterial1315.
• In this embodiment, the[0423]bounded region1325 of thepocket1300 comprises a portion of theperiphery1318 of the layer ofmaterial1315. Thebounded region1325 of thepocket1300 comprises thefirst side1340 and thesecond side1341 of the layer ofmaterial1315. Thecenter1326 of thepocket1300 comprises themiddle portion1319 of the layer ofmaterial1315. Theopening1310 of thepocket1300 comprises thethird side1342 of the layer ofmaterial1315 and thetop surface1331 of the moldedcover220. Thebounded region1325 of thepocket1300 is curved around thecenter1326 of thepocket1300. Thebounded region1325 of thepocket1300 does not completely enclose thecenter1326.
• In this embodiment, the[0424]bounded region1325 of the pocket comprises a contiguous portion of theperiphery1318 of the layer ofmaterial1315. In an alternate embodiment, thebounded region1325 of the pocket comprises a plurality of segmented portions of theperiphery1318 of the layer ofmaterial1315.
• In an alternate embodiment the[0425]bounded region1325 of thepocket1300 does not comprise any portion of theperiphery1318 of the layer ofmaterial1315.
• FIGS.[0426]38(a)-38(c) illustrates a lead electrodeassembly manipulation tool927. The lead electrodeassembly manipulation tool927 illustrated is useful for manipulating alead electrode assembly100 having apocket1300 during the implantation of thelead electrode assembly100 in a patient. Examples of such alead electrode assembly100 embodiments are shown in FIGS.36(a),36(b),37(a) and37(b).
• FIG. 38([0427]a) is a top view of the lead electrodeassembly manipulation tool927 of this embodiment. The lead electrodeassembly manipulation tool927 comprises a handle1142 (not shown), arod1144 and apaddle1350.
• The[0428]rod1144 and handle1142 are substantially similar to therod1144 and handle1142 of the lead electrodeassembly manipulation tool927 illustrated in FIGS.35(a)-35(d). Thehandle1142 is connected to therod1144.
• The[0429]paddle1350 is attached to thedistal end1148 of therod1144. Thepaddle1350 comprises adisk1351 and a tang1161 (phantom view).
• FIG. 38([0430]b) is a side view of the lead electrodeassembly manipulation tool927 of this embodiment. Thetang1161 is inserted in theslot1162 in therod1144. Thetang1161 is welded into theslot1162 of therod1144.
• The[0431]disk1351 and thetang1161 are punched from a single sheet of steel having a thickness of approximately 3 mm. In other embodiments, thedisk1351 andtang1161 are composed of titanium, a polymeric material or any other material suitable for this purpose. In one embodiment, thehandle1142, therod1144 and thepaddle1350 are all made from the same piece of material.
• We now turn to FIG. 38([0432]c) for a description of the use of the lead electrodeassembly manipulation tool927 in the implantation of alead electrode assembly100 into a patient.
• As discussed with reference to FIG. 31, an[0433]incision905 is made in the patient900. As discussed with reference to FIG. 32(a), asubcutaneous path1090 is created in the patient900 with ahemostat932.
• The[0434]lead electrode assembly100 is then captured by the lead electrodeassembly manipulation tool927. Thepaddle1350 of the lead electrodeassembly manipulation tool927 is inserted into thepocket1300 of thelead electrode assembly100. Thepaddle1350 is slid into theinterior1305 of the pocket via theopening1310 of the pocket until it can go no further. At this point, thepaddle1350 touches the inner surface1316 of theproximal end1321 of the layer ofmaterial1315.
• The[0435]lead21 of thelead electrode assembly100 can then be pulled toward thehandle1142 of the lead electrodeassembly manipulation tool927 until it is taught. This acts to prevent thepaddle1350 of the lead electrodeassembly manipulation tool927 from sliding out of thepocket1300 of thelead electrode assembly100.
• The lead electrode[0436]assembly manipulation tool927 may then be used to place thelead electrode assembly100 into theincision905 of the patient as seen in FIG. 31. The lead electrodeassembly manipulation tool927 may then be used to move theelectrode107 to thetermination point1085 of thesubcutaneous path1090 created as discussed with reference to FIG. 32(c).
• The[0437]lead electrode assembly100 is then released from the lead electrodeassembly manipulation tool927. To achieve this, thelead21 of thelead electrode assembly100 is released so that thepaddle1350 can slide relative to thepocket1300 of thelead electrode assembly100. The lead electrodeassembly manipulation tool927 may then be extracted from thesubcutaneous path1090 leaving thelead electrode assembly100 behind.
• Alternately, a curved hemostat, such as the[0438]hemostat930 discussed with reference to FIG. 32(b) could be inserted in thepocket1300 of thelead electrode assembly100. The hemostat could then be used to move theelectrode107 to thetermination point1085 of thesubcutaneous path1090 as discussed above.
• Alternately, a curved hemostat, such as the[0439]hemostat930 discussed with reference to FIG. 32(b) could be used to grip thepocket1300 of thelead electrode assembly100, and used to move theelectrode107 to thetermination point1085 of thesubcutaneous path1090 as discussed above.
• FIGS.[0440]39(a)-39(b) illustrate an alternative embodiment of thelead electrode assembly100. This embodiment is substantially similar to the embodiment illustrated in FIGS.38(a)-38(c). Thebacking layer130 of this embodiment, however, lacks apocket1300. Moreover, thelead electrode assembly100 of this embodiment further comprises afirst channel guide1401 and asecond channel guide1402.
• FIG. 39([0441]a) illustrates a cross-sectional rear plan view of thelead electrode assembly100 of this embodiment. Thefirst channel guide1401 and asecond channel guide1402 each have an interior1403 and anopening1404.
• The[0442]first channel guide1401 and thesecond channel guide1402 each comprise a strip of material1406 attached to the moldedcover220.
• The strip of[0443]material1406 comprising thefirst channel guide1401 is substantially rectangular in shape. The strip ofmaterial1406 comprises afirst side1410 and asecond side1412. Thefirst side1410 and thesecond side1412 of the strip ofmaterial1406 are parallel to each other. In another embodiment, thefirst side1410 of the strip ofmaterial1406 is not parallel to thesecond side1412.
• The strip of material[0444]1406 further comprises aninner surface1417 and aouter surface1416. The strip of material is positioned so that theinner surface1417 of thefirst side1410 faces theouter surface1330 of the moldedcover220. Thefirst side1410 of the strip of material is attached to thefirst side1333 of thetop surface1331 of the moldedcover220. Thesecond side1412 of the strip ofmaterial1406 is attached to theskirt222 of the moldedcover220.
• The[0445]interior1403 of the first channel guide is formed between theinner face1417 of the strip ofmaterial1406 and theouter surface1330 of the moldedcover220.
• The second channel guide is formed in substantially the same way on the[0446]second side1334 of the moldedcover220.
• FIG. 39([0447]b) illustrates a top plan view of the lead electrode assembly of the embodiment of FIG. 39(a). The strip ofmaterial1406 comprising thefirst channel guide1401 is substantially rectangular in shape having adistal end1413 and aproximal end1414. Thedistal end1413 and theproximal end1414 of the strip ofmaterial1406 are parallel to each other. In another embodiment, thedistal end1413 of the strip ofmaterial1406 is not parallel to theproximal end1414 of the strip ofmaterial1406.
• The[0448]opening1404 of thefirst channel guide1401 is formed by thedistal end1413 of the strip ofmaterial1406 and theouter surface1330 of the moldedcover220.
• The[0449]first side1410 and the second side1412 (not shown) of the strip ofmaterial1406 comprising thefirst channel guide1401 are positioned so that they lie parallel to the first side1333 (phantom view) of the moldedcover220.
• The[0450]second channel guide1402 is formed and mounted to thelead electrode assembly100 in substantially the same way as thefirst channel guide1401. Thefirst side1410 and the second side1412 (not shown) of the strip ofmaterial1406 comprising thesecond channel guide1402 are positioned so that they lie parallel to the second side1333 (phantom view) of the moldedcover220.
• The strips of[0451]material1406 are composed of polyurethane. In an alternate embodiment, the strips ofmaterial1406 are composed of any polymeric material. The strips ofmaterial1406 are fastened to the moldedcover220 withstitching360.
• In an alternate embodiment, the strips of[0452]material1406 are made of molded silicone and attached to the moldedcover220 by fusing them to the moldedcover220. In an alternate embodiment, thefirst channel guide1401 and thesecond channel guide1402 are formed as part of the moldedcover220.
• FIGS.[0453]40(a)-40(b) illustrates a lead electrodeassembly manipulation tool927. The lead electrodeassembly manipulation tool927 illustrated is useful for manipulating alead electrode assembly100 having afirst channel guide1401 and asecond channel guide1402 during the implantation of thelead electrode assembly100 in a patient. Examples of such alead electrode assembly100 embodiments are shown in FIGS.39(a)-39(b).
• FIG. 40([0454]a) illustrates a top plan view of a lead electrodeassembly manipulation tool927. The lead electrodeassembly manipulation tool927 in this embodiment comprises a handle1142 (not shown), arod1144 and a channel guide fork1446.
• The[0455]rod1144 and handle1142 are substantially similar to therod1144 and handle1142 of the lead electrodeassembly manipulation tool927 illustrated in FIGS.35(a)-35(d). Thehandle1142 is connected to therod1144.
• The channel guide fork[0456]1446 is attached to thedistal end1148 of therod1144. The channel guide fork1446 comprises a pair oftines1451 separated by agap1455 and atine base1450 having atang1161.
• The pair of[0457]tines1451 each have aproximal end1452 and adistal end1453. The proximal ends1452 of the pair oftines1451 are attached to thetine base1450. The pair oftines1451 have a substantially cylindrical form. Thedistal end1453 of each of the pair oftines1451 is rounded.
• The length of the pair of[0458]tines1451 is substantially equal to the length of thefirst side1410 of the strips of material1406 comprising thefirst channel guide1401 andsecond channel guide1402. In alternate embodiments, the length of thetines1451 is substantially greater than or less than the length of thefirst side1410 of the strips of material1406 comprising thefirst channel guide1401 andsecond channel guide1402.
• The tines are separated by a[0459]gap1455 between the proximal ends1452 of the pair oftines1451. The pair oftines1451 are substantially straight and substantially parallel to each other.
• The[0460]tine base1450 connects the pair oftines1451 to thedistal end1148 of therod1144. Thetine base1450 comprises a tang1161 (phantom view). Thetang1161 is inserted in aslot1162 in therod1144. Thetang1161 is welded in theslot1162 of therod1144.
• The pair of[0461]tines1451 comprising the channel guide fork1446 are composed of steel and have a diameter of approximately 3 mm. Thetine base1450 comprising the channel guide fork1446 is punched from a single strip of steel having a thickness of approximately 3 mm. The pair oftines1451 are welded to thetine base1450.
• In other embodiments, the channel guide fork[0462]1446 is composed of metal, a polymeric material, or any other material suitable for this purpose. In one embodiment, thehandle1142, therod1144 and the channel guide fork1446 are all made from the same piece of material.
• We now turn to FIG. 40([0463]b) for a description of the use of the lead electrodeassembly manipulation tool927 in the implantation of alead electrode assembly100 into a patient.
• As discussed with reference to FIG. 31, an[0464]incision905 is made in the patient900. As discussed with reference to FIG. 32(a), asubcutaneous path1090 is created in the patent900 with ahemostat932.
• The[0465]lead electrode assembly100 is then captured by the lead electrodeassembly manipulation tool927. The pair oftines1451 of the lead electrodeassembly manipulation tool927 is inserted into theopenings1404 in thefirst channel guide1401 andsecond channel guide1402.
• The[0466]electrode107 is placed into thegap1455 between the tines of the channel guide fork1446. Thetines1451 fit into theinterior1403 of thefirst channel guide1401 andsecond channel guide1402. The molded cover is slid toward theproximal end1452 of the tines until it can go no further. Thelead21 of thelead electrode assembly100 can then be pulled in toward thehandle1142 of the lead electrodeassembly manipulation tool927 until it is taught. This acts to prevent thelead electrode assembly100 from sliding toward thedistal end1453 of the pair oftines1451 of the channel guide fork1446.
• The lead electrode[0467]assembly manipulation tool927 may then be used to place thelead electrode assembly100 into theincision905 of the patient as seen in FIG. 31. The lead electrodeassembly manipulation tool927 may then be used to move theelectrode107 through thetermination point1085 of thesubcutaneous path1090 created as discussed with reference to FIG. 32(c).
• The[0468]lead electrode assembly100 is then released from the lead electrodeassembly manipulation tool927. To achieve this, thelead21 of thelead electrode assembly100 is released so that the pair oftines1451 of the channel guide fork1446 of the lead electrodeassembly manipulation tool927 can slide relative to thefirst channel guide1401 andsecond channel guide1402 of thelead electrode assembly100. The lead electrodeassembly manipulation tool927 may then be extracted from thesubcutaneous path1090 leaving thelead electrode assembly100 behind.
• FIG. 41([0469]a) illustrates a subcutaneous implantable cardioverter-defibrillator kit1201 of the present invention. The kit comprises a group of items that may be used in implanting a S-ICD system in a patient. The kit1201 comprises a group of one or more of the following items: an S-ICD canister11, alead electrode assembly100, ahemostat1205, a lead electrodeassembly manipulation tool927, a medical adhesive1210, an anesthetic1215, a tube ofmineral oil1220 and a tray1200 for storing these items.
• In one embodiment, the S-[0470]ICD canister11 is the S-ICD canister11 seen in, and discussed with reference to FIG. 1.
• The[0471]lead electrode assembly100 is thelead electrode assembly100 with arail1100, and discussed with reference to FIGS.33(b) and33(c). In alternate embodiments, thelead electrode assembly100 is anylead electrode assembly100 including anelectrode107 with anappendage118; a pocket; or a first and second channel guide for positioning theelectrode107 during implantation.
• The[0472]hemostat1205 is a curved hemostat made of steel having afirst end1240 and asecond end1241. Thehemostat1205 has a length, measured between thefirst end1240 and thesecond end1241 as shown in FIG. 41(b) by dimension L_Hemostat. The length of thehemostat1205, L_Hemostat, is approximately 75 cm. In an alternate embodiments, thehemostat1205 is a length other than 75 cm. In an alternate embodiment, thehemostat1205 is the enhanced hemostat seen in, and discussed with reference to FIG. 31.
• The lead electrode[0473]assembly manipulation tool927 is the lead electrodeassembly manipulation tool927 with arail fork1146. In alternate embodiments, the lead electrodeassembly manipulation tool927 is any lead electrodeassembly manipulation tool927 including a paddle or a channel guide fork.
• The medical adhesive[0474]1210 comprises a roll of clear, 1-inch wide medical adhesive tape. As will be recognized, the medical adhesive could be a liquid adhesive, or any other adhesive substance.
• The[0475]anesthetic1215 is a one ounce tube of lidocaine gel. This can be used as a local anesthetic for the introduction of thelead electrode assembly100 as discussed below. As will be recognized, the anesthetic could be any substance that has a pain-killing effect. Alternatively, one could use an injectable form of anesthetic inserted along the path of the lead.
• The tube of[0476]mineral oil1220 is a one ounce tube of mineral oil. This can be used for oiling parts of theelectrode connector block17 seen in FIG. 1.
• The tray[0477]1200 is a box sized to fit the items of the kit1201. The tray1200 is composed of molded plastic. In another embodiment, the tray1200 is a cardboard box. One skilled in the art will recognize that the tray1200 may comprise any container capable of containing the items of the kit. In one embodiment, the tray is formed with recessedpartitions1230 that generally follow the outline of the items of the kit1201 to be stored in the tray. In one embodiment, the tray1200 haspackaging material1225 disposed over it, wherein thepacking material1225 provides a sanitary cover for the items of the kit1201. Thepackaging material1225 further acts to contain the items of the kit1201.
• In an alternate embodiment the kit[0478]1201 comprises tenlead electrode assemblies100 each comprising a lead21 having a lead length, l_Lead, different from the others. In one embodiment, the lead lengths range between approximately 5 cm and approximately 52 cm with approximately a 10 cm difference between the lead length of eachlead electrode assembly100.
• In an alternative embodiment, the kit[0479]1201 comprises an S-ICD canister11, ahemostat1205 and an assortment oflead electrode assemblies100 each comprising a lead21 having a lead length, l_Lead, different from the others.
• In one embodiment, the kit[0480]1200 further comprises a tray1201 and an assortment oflead electrode assemblies100, each with anelectrode107 curved at a radius r different from the others.
• In another embodiment, the kit[0481]1200 includes components sized for surgery on a patient of a particular size. A kit1200 for a 10 year old child, for example, includes an S-ICD canister11 with a length of approximately 10 cm, alead electrode assembly100 with a lead length, L_Leadof approximately 12 cm and a radius r of approximately 10 cm andhemostat1205 with a hemostat length, L_Hemostat, of approximately 12 cm.
• The S-ICD device and method of the present invention may be embodied in other specific forms without departing from the teachings or essential characteristics of the invention. The described embodiments are therefore to be considered in all respects as illustrative and not restrictive, the scope of the invention being indicated by the appended claims rather than by the foregoing description and all changes which come within the meaning and range of equivalency of the claims are therefore to be embraced therein.[0482]

Claims (58)

What is claimed is:

1. A lead electrode assembly for use with an implantable cardioverter-defibrillator subcutaneously implanted outside a patient's ribcage between the third and twelfth ribs, wherein the lead electrode assembly comprises an electrode.

2. The lead electrode assembly ofclaim 1, wherein the electrode can emit an effective energy for shocking the patient's heart.

3. The lead electrode assembly ofclaim 2, wherein the effective energy for shocking the patient's heart is approximately 0.5 J to approximately 350 J.

4. The lead electrode assembly ofclaim 3, wherein the effective energy for shocking the patient's heart is approximately 0.5 J to approximately 25 J.

5. The lead electrode assembly ofclaim 3, wherein the effective energy for shocking the patient's heart is approximately 150 J to approximately 200 J.

6. The lead electrode assembly ofclaim 3, wherein the effective energy for shocking the patient's heart is approximately 200 J to approximately 250 J.

7. The lead electrode assembly ofclaim 3, wherein the effective energy for shocking the patient's heart is approximately 250 J to approximately 300 J.

8. The lead electrode assembly ofclaim 3, wherein the effective energy for shocking the patient's heart is approximately 300 J to approximately 350 J.

9. The lead electrode assembly ofclaim 1, wherein the electrode is between approximately 100 square millimeters to approximately 5000 square millimeters in area.

10. The lead electrode assembly ofclaim 9, wherein the electrode is between approximately 1000 square millimeters to approximately 1500 square millimeters in area.

11. The lead electrode assembly ofclaim 9, wherein the electrode is between approximately 1500 square millimeters to approximately 2000 square millimeters in area.

12. The lead electrode assembly ofclaim 9, wherein the electrode is between approximately 2000 square millimeters to approximately 2500 square millimeters in area.

13. The lead electrode assembly ofclaim 9, wherein the electrode is between approximately 2500 square millimeters to approximately 3000 square millimeters in area.

14. The lead electrode assembly ofclaim 9, wherein the electrode is between approximately 3000 square millimeters to approximately 3500 square millimeters in area.

15. The lead electrode assembly ofclaim 9, wherein the electrode is between approximately 3500 square millimeters to approximately 4000 square millimeters in area.

16. The lead electrode assembly ofclaim 9, wherein the electrode is between approximately 4000 square millimeters to approximately 4500 square millimeters in area.

17. The lead electrode assembly ofclaim 9, wherein the electrode is between approximately 4500 square millimeters to approximately 5000 square millimeters in area.

18. An implantable cardioverter-defibrillator for subcutaneous positioning between the third rib and the twelfth rib within a patient, the implantable cardioverter-defibrillator comprising:

a housing;

an electrical circuit located within the housing;

a first electrode coupled to the electrical circuit and located on the housing; and

a lead electrode assembly coupled to the housing, wherein the lead electrode assembly comprises:

a second electrode coupled to the electrical circuit.

19. The implantable cardioverter-defibrillator ofclaim 18, wherein the second electrode can emit an effective energy for shocking the patient's heart.

20. The implantable cardioverter-defibrillator ofclaim 19, wherein the effective energy for shocking the patient's heart is approximately 0.5 J to approximately 350 J.

21. The implantable cardioverter-defibrillator ofclaim 20, wherein the effective energy for shocking the patient20 heart is approximately 0.5 J to approximately 25 J.

22. The implantable cardioverter-defibrillator ofclaim 20, wherein the effective energy for shocking the patient's heart is approximately 150 J to approximately 200 J.

23. The lead electrode assembly ofclaim 20, wherein the effective energy for shocking the patient's heart is approximately 200 J to approximately 250 J.

24. The lead electrode assembly ofclaim 20, wherein the effective energy for shocking the patient's heart is approximately 250 J to approximately 300 J.

25. The lead electrode assembly ofclaim 20, wherein the effective energy for shocking the patient's heart is approximately 300 J to approximately 350 J.

26. The implantable cardioverter-defibrillator ofclaim 18, wherein the second electrode is between approximately 100 square millimeters to approximately 5000 square millimeters in area.

27. The implantable cardioverter-defibrillator ofclaim 26, wherein the second electrode is between approximately 1000 square millimeters to approximately 1500 square millimeters in area.

28. The implantable cardioverter-defibrillator ofclaim 26, wherein the second electrode is between approximately 1500 square millimeters to approximately 2000 square millimeters in area.

29. The implantable cardioverter-defibrillator ofclaim 26, wherein the second electrode is between approximately 2000 square millimeters to approximately 2500 square millimeters in area.

30. The implantable cardioverter-defibrillator ofclaim 26, wherein the second electrode is between approximately 2500 square millimeters to approximately 3000 square millimeters in area.

31. The implantable cardioverter-defibrillator ofclaim 26, wherein the second electrode is between approximately 3000 square millimeters to approximately 3500 square millimeters in area.

32. The implantable cardioverter-defibrillator ofclaim 26, wherein the second electrode is between approximately 3500 square millimeters to approximately 4000 square millimeters in area.

33. The implantable cardioverter-defibrillator ofclaim 26, wherein the second electrode is between approximately 4000 square millimeters to approximately 4500 square millimeters in area.

34. The implantable cardioverter-defibrillator ofclaim 26, wherein the second electrode is between approximately 4500 square millimeters to approximately 5000 square millimeters in area.

35. An implantable cardioverter-defibrillator for subcutaneous positioning between the third rib and the twelfth rib within a patient, the implantable cardioverter-defibrillator comprising:

a housing; and

a lead electrode assembly coupled to the housing, wherein the lead electrode assembly comprises:

an electrode.

36. The implantable cardioverter-defibrillator ofclaim 35, wherein the electrode can emit an effective energy for shocking the patient's heart.

37. The implantable cardioverter-defibrillator ofclaim 36, wherein the effective energy for shocking the patient's heart is approximately 0.5 J to approximately 350 J.

38. The implantable cardioverter-defibrillator ofclaim 37, wherein the effective energy for shocking the patient's heart is approximately 0.5 J to approximately 25 J.

39. The implantable cardioverter-defibrillator ofclaim 37, wherein the effective energy for shocking the patient's heart is approximately 150 J to approximately 200 J.

40. The implantable cardioverter-defibrillator ofclaim 37, wherein the effective energy for shocking the patient's heart is approximately 200 J to approximately 250 J.

41. The implantable cardioverter-defibrillator ofclaim 37, wherein the effective energy for shocking the patient's heart is approximately 250 J to approximately 300 J.

42. The implantable cardioverter-defibrillator ofclaim 37, wherein the effective energy for shocking the patient's heart is approximately 300 J to approximately 350 J.

43. The implantable cardioverter-defibrillator ofclaim 35, wherein the electrode is between approx00imately 100 square millimeters to approximately 5000 square millimeters in area.

44. The implantable cardioverter-defibrillator ofclaim 43, wherein the electrode is between approximately 1000 square millimeters to approximately 1500 square millimeters in area.

45. The implantable cardioverter-defibrillator ofclaim 43, wherein the electrode is between approximately 1500 square millimeters to approximately 2000 square millimeters in area.

46. The implantable cardioverter-defibrillator ofclaim 43, wherein the electrode is between approximately 2000 square millimeters to approximately 2500 square millimeters in area.

47. The implantable cardioverter-defibrillator ofclaim 43, wherein the electrode is between approximately 2500 square millimeters to approximately 3000 square millimeters in area.

48. The implantable cardioverter-defibrillator ofclaim 43, wherein the electrode is between approximately 3000 square millimeters to approximately 3500 square millimeters in area.

49. The implantable cardioverter-defibrillator ofclaim 43, wherein the electrode is between approximately 3500 square millimeters to approximately 4000 square millimeters in area.

50. The implantable cardioverter-defibrillator ofclaim 43, wherein the electrode is between approximately 4000 square millimeters to approximately 4500 square millimeters in area.

51. The implantable cardioverter-defibrillator ofclaim 43, wherein the electrode is between approximately 4500 square millimeters to approximately 5000 square millimeters in area.

52. The implantable cardioverter-defibrillator ofclaim 35, wherein the implantable cardioverter-defibrillator is positioned subcutaneously between the third and fifth ribs.

53. The implantable cardioverter-defibrillator ofclaim 35, wherein the implantable cardioverter-defibrillator is positioned subcutaneously between the fourth and sixth ribs.

54. The implantable cardioverter-defibrillator ofclaim 35, wherein the implantable cardioverter-defibrillator is positioned subcutaneously between the sixth and eighth ribs.

55. The implantable cardioverter-defibrillator ofclaim 35, wherein the implantable cardioverter-defibrillator is positioned subcutaneously between the eighth and tenth ribs.

56. The implantable cardioverter-defibrillator ofclaim 35, wherein the implantable cardioverter-defibrillator is positioned subcutaneously between the tenth and twelfth ribs

57. The implantable cardioverter-defibrillator ofclaim 35, wherein the implantable cardioverter-defibrillator provides anti-tachycardia pacing energy to the heart for treatment of atrial fibrillation.

58. The implantable cardioverter-defibrillator ofclaim 35, wherein the implantable cardioverter-defibrillator provides anti-tachycardia pacing energy to the heart for treatment of ventricular tachycardia.

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