BACKGROUND
1. Technical Field
The present disclosure relates to electrode thermosurgery systems and, more particularly, to cool-tip ablation electrode systems used for thermosurgery procedures and the like.
2. Background of Related Art
Therapeutic lesions in living bodies have been accomplished for many decades using radio-frequency (RF) and other forms of energy. The procedures have been particularly useful in the field of neurosurgery, typically where RF ablation needle electrodes (usually of elongated cylindrical geometry) are inserted into a living body. A typical form of such needle electrodes incorporates an insulated sheath from which an exposed (uninsulated) tip extends.
Generally, the ablation electrode is coupled between a grounded RF power source (outside the body) and a reference ground or indifferent electrode for contacting a large surface of the body. When an RF voltage is provided between the reference electrode and the inserted ablation electrode, RF current flows from the needle electrode through the body. Typically, the current density is very high near the tip of the needle electrode, which heats and destroys the adjacent tissue.
In the past, RF ablation electrode systems have incorporated temperature sensors, for example, in the form of a thermistor or thermocouple. In that regard, reference may be made to U.S. Pat. No. 4,411,266 to Cosman, the entire contents of which are incorporated herein by reference, for a detailed discussion of the same. Typically, the sensor is connected to a monitoring apparatus for indicating temperature to assist in accomplishing a desired lesion. As generally known, for a given tip geometry and tip temperature, lesions of a prescribed size can be made quite consistently.
Over the years, a wide variety of RF electrode shapes and configurations have been used, for example, several current forms are available from Radionics, Inc., located in Burlington, Mass. Such electrodes have been used to accomplish lesions in a wide variety of targets within the body, including the brain, the spinal column and the heart.
However, a limitation of prior electrode ablation systems relates to the temperature of the tip. Specifically, prior needle electrodes of a given tip geometry never should effectively exceed a temperature of 100° C. At that temperature, the surrounding tissue will boil and char. Also, uncontrolled disruption, such as hemorrhage and explosive gas formation, may cause extremely hazardous and clinically dangerous effects on the patient. Consequently, the lesion size for a given electrode geometry generally has been considered to be somewhat limited by the fact that the tissue near the tip must not exceed 100° C.
Essentially, during RF ablation, the needle electrode temperature is highest near the tip, because the current density is the highest at that location. Accordingly, temperature falls off as a function of distance from the tip of the needle electrode, and except for possible abnormalities in tissue conductivity and so on, in a somewhat predictable and even calculable pattern. As an attendant consequence, the size of RF lesions for a given electrode geometry have been somewhat limited.
One proposed solution to the limitation of lesion's size has been to employ “off-axis” electrodes, for example the so called Zervas Hypophysectomy Electrode or the Gildenberg Side-Outlet electrode, as manufactured by Radionics, Inc., Burlington, Mass. However, such systems, in requiring multiple tissue punctures, increase the risk of hemorrhage, severely prolong the time of surgery and increase the level of delicacy. Also, an umbrella of off-axis lesions may not produce a desired homogenous or uniform lesion.
Accordingly, a need exists for an ablation electrode system capable of accomplishing enlarged lesions (radius and volume).
A need also exists for an ablation electrode system which is economical to manufacture and assemble.
SUMMARY
The present disclosure relates to ablation electrode systems used for thermosurgery procedures and the like.
According to one aspect of the present disclosure, an ablation electrode system for use with a source of electrosurgical energy to ablate tissue in a living subject is provided. The ablation electrode system includes a handle assembly; and a needle electrode assembly supported in and extending from the handle assembly. The needle electrode assembly includes an outer tube having at least a conductive distal tip, a proximal end portion supported in the handle assembly, and defining a cavity therein; and an inner tube disposed at least partially within the cavity of the outer tube and having a proximal end portion supported within the handle assembly, the inner tube defining a lumen therein.
The ablation electrode system further includes a hub assembly supported within the handle assembly and fluidly connected to the needle electrode assembly. The hub assembly includes an outer shell defining a lumen therein; and an inner manifold operatively supported in the lumen of the outer shell. The inner manifold and the outer shell are configured and dimensioned so as to define a first chamber and a second chamber therebetween. The proximal end portion of the inner tube is in fluid communication with the first chamber and the proximal end portion of the outer tube is in fluid communication with the second chamber.
The ablation electrode system further includes an electrical conduit electrically connected to the outer tube of the needle electrode assembly; a first fluid conduit fluidly connected to the first chamber; and a second fluid conduit fluidly connected to the second chamber.
It is envisioned that the outer tube of the needle electrode assembly is fabricated from an electrically conductive material. A layer of insulative material may be disposed on an outer surface of the outer tube. The distal tip of the outer tip may be exposed.
The inner tube may deliver fluid to the distal tip of the outer tube.
The ablation electrode assembly may further include a thermocouple assembly electrically connected to the inner tube. The thermocouple assembly may include a constantan wire extending through the lumen of the inner tube and electrically connected to a distal end of the inner tube.
The inner manifold may define a lumen therein interconnecting the second chamber of the hub assembly to the second fluid conduit.
An adhesive may be applied to a proximal end of the inner manifold and the outer shell to at least one of secure the inner manifold within the outer shell and seal the hub assembly from fluid leaks from between the outer shell and the inner manifold. A seal element may be provided between the outer shell and the inner manifold of the hub assembly to prevent transmission of fluid between the first chamber and the second chamber.
The ablation electrode assembly may further include a plurality of needle electrode assemblies supported in and extending from the handle assembly. A proximal end portion of each inner tube is in fluid communication with the first chamber and a proximal end portion of each outer tube is in fluid communication with the second chamber. The thermocouple assembly may include a constantan wire extending through the lumen of at least one inner tube and electrically connected to a distal end of said at least one inner tube.
According to another aspect of the present disclosure, an ablation electrode system is provided and includes a handle assembly; a needle electrode assembly supported in and extending from the handle assembly. The needle electrode assembly includes an outer tube having at least a conductive distal tip, a proximal end portion supported in the handle assembly, and defining a cavity therein; and an inner tube disposed at least partially within the cavity of the outer tube and having a proximal end portion supported within the handle assembly, the inner tube defining a lumen therein.
The ablation electrode assembly includes a hub assembly supported within the handle assembly and fluidly connected to the needle electrode assembly. The hub assembly defines a first chamber and a second chamber; wherein the proximal end portion of the inner tube is in fluid communication with the first chamber and the proximal end portion of the outer tube is in fluid communication with the second chamber.
The ablation electrode assembly includes an electrical conduit electrically connected to the outer tube of the needle electrode assembly; a first fluid conduit fluidly connected to the first chamber; and a second fluid conduit fluidly connected to the second chamber.
The inner manifold defines a lumen therein interconnecting the second chamber of the hub assembly to the second fluid conduit. The hub assembly includes an outer shell defining a lumen therein and an inner manifold operatively supported in the lumen of the outer shell.
According to yet another aspect of the present disclosure, an ablation system for ablating tissue in a living subject is provided. The ablation system includes an ablation electrode system including a needle electrode assembly. The needle electrode assembly includes an outer tube having at least a conductive distal tip and defining a cavity therein; and an inner tube disposed at least partially within the cavity of the outer tube and defining a lumen therein.
The ablation electrode system further includes a hub assembly fluidly connected to the needle electrode assembly. The hub assembly defines a first chamber and a second chamber; wherein a proximal end portion of the inner tube is in fluid communication with the first chamber and a proximal end portion of the outer tube is in fluid communication with the second chamber.
The ablation system includes a source of electrosurgical energy; a source of fluid; an electrical conduit electrically interconnecting the outer tube of the needle electrode assembly and the source of electrosurgical energy; a first fluid conduit fluidly interconnecting the source of fluid and the first chamber; and a second fluid conduit fluidly connected to the second chamber.
For a better understanding of the present invention and to show how it may be carried into effect, reference will be made by way of example to the accompanying drawings.
BRIEF DESCRIPTION OF THE DRAWINGS
In the drawings, which constitute a part of the specification, exemplary embodiments exhibiting various objectives and features hereof are set forth, specifically:
FIG. 1 is a perspective view of an ablation electrode system in accordance with an embodiment of the present disclosure;
FIG. 2 is an enlarged perspective view of the ablation electrode system of FIG. 1, with a handle half-section removed therefrom and a hub assembly disposed therein shown partially broken away;
FIG. 3 is a longitudinal cross-sectional view of the ablation electrode system of FIGS. 1 and 2;
FIG. 4 is an enlarged longitudinal cross-sectional view of the hub assembly of FIGS. 2 and 3;
FIG. 5 is a longitudinal cross-sectional view of the outer shell of the hub assembly of FIGS. 2-4, including a needle electrode shown operative connected thereto;
FIG. 6 is a perspective view an inner manifold of the hub assembly of FIGS. 2-4;
FIG. 7 is a longitudinal cross-sectional view of the inner manifold of FIG. 6;
FIG. 8 is a perspective view of an ablation electrode system according to an alternate embodiment of the present disclosure;
FIG. 9 is a longitudinal cross-sectional view of the ablation electrode system of FIG. 8;
FIG. 10 is a longitudinal cross-sectional view of the outer shell of the hub assembly of FIG. 9, including needle electrodes shown operative connected thereto;
FIG. 10A is a distal end view of the outer shell of the hub assembly of the ablation electrode system of FIG. 8;
FIG. 11 is a perspective view an inner manifold of the hub assembly of FIG. 9;
FIG. 12 is a longitudinal cross-sectional view of the inner manifold of FIG. 11;
FIG. 13 is a perspective view of an ablation electrode system illustrating a strain relief member operatively associated therewith for support of the cables and/or conduits entering the handle;
FIG. 14 is a schematic perspective view of a strain relief member for use with ablation electrode system;
FIG. 15 is a schematic longitudinal cross-sectional view of another strain relief member shown supported in the handle of the ablation electrode system;
FIG. 16 is a schematic longitudinal cross-sectional view of yet another strain relief member shown supported in the handle of the ablation electrode system;
FIG. 17 is a schematic perspective view of another strain relief member for use with ablation electrode system; and
FIG. 18 is a cross-sectional view of the strain relief member of FIG. 17, as taken through 18-18 of FIG. 17.
DETAILED DESCRIPTION OF EMBODIMENTS
Embodiments of ablation electrode systems, in accordance with the present disclosure, will now be described in detail with reference to the drawings figures wherein like reference numerals identify similar or identical structural elements. As shown in the drawings and described throughout the following description, as is traditional when referring to relative positioning on a surgical instrument, device or apparatus, the term “proximal” refers to the end of the instrument, apparatus or device which is closer to the user and the term “distal” refers to the end of the apparatus which is further away from the user.
Referring initially to FIGS. 1-7, an electrode ablation system, according to an embodiment of the present disclosure, is generally designated as ablation system 100. Ablation system 100 includes a housing or handle assembly 110, and at least one needle electrode assembly 150 supported within and extending from housing assembly 110. Housing assembly 110 and needle electrode assembly 150 define a central longitudinal axis “X”.
As seen in FIGS. 1-3, housing assembly 110 includes a housing or handle 112 having first half-section 112a and a second half-section 112b selectively connectable to one another (e.g., in a snap-fit manner) via connecting structure 114 or the like. Desirably, housing 112 has a substantially conical shape defining a flattened proximal surface 116a and a flattened distal surface 116b (FIGS. 2 and 3). Housing 112 further includes an annular ramp-like structure 116c extending from the surface thereof. Ramp-like structure 116c acts as a surface against which an operators fingers contact for distal advancement of needle electrode 150 into the patient and/or proximal withdrawal of needle electrode 150 from the patient.
As seen in FIGS. 2-8, electrode ablation system 100 further includes a hub assembly 120 operatively supported in housing 112 of housing assembly 110. Hub assembly includes a hub assembly outer shell 130 and a hub assembly inner manifold 140 operative disposed within outer shell 130. Desirably, outer shell 130 and inner manifold 140 of hub assembly are each fabricated from an electrically non-conductive material or the like.
As seen in FIGS. 2-5, hub assembly outer shell 130 includes a body portion 132 defining a central lumen 134 extending therethrough. Desirably, outer shell 130 defines a central longitudinal axis “X1” extending through central lumen 134. Preferably, when outer shell 130 is positioned in housing 112, the central longitudinal “X1” axis thereof at least substantially aligns with the central longitudinal “X” axis of housing 112 and needle electrode assembly 150. Central lumen 134 of outer shell 130 includes a tapered distal end 136 defining a constricted passage 134a therethrough. Desirably, passage 134a is sized to support and receive needle electrode assembly 150 therein.
Body portion 132 of outer shell 130 may include an annular flange 138 formed therearound. As seen in FIGS. 2 and 3, annular flange 138 of outer shell 130 is receiveable in a complementary annular channel or groove 118 formed or provided in housing 112. Accordingly, annular flange 138 and annular groove 118 cooperate to fix the location of hub assembly 120 relative to housing 112.
As seen in FIGS. 2-4, 6 and 7, inner manifold 140 is configured and dimensioned for support within lumen 134 of outer shell 130 Inner manifold 140 includes a body portion 142 defining a first or inflow lumen 144a formed at least partially in a proximal end portion 142b thereof. Inner manifold 140 further includes a second or outflow lumen 144b extending entirely therethrough. Inner manifold 140 further includes a third lumen 144c formed at least partially in a distal end portion 142a thereof.
As seen in FIGS. 3, 4, 6 and 7, inner manifold 140 defines a first recess 148 formed therein such that when inner manifold 140 is inserted into lumen 134 of outer shell 130, first recess 148 defines a first cavity or chamber 122 between outer shell 130 and inner manifold 140. As seen in FIGS. 3 and 4, first lumen 144a and third lumen 144c are each in fluid communication with first chamber 122.
With continued reference to FIGS. 3 and 4, when inner manifold 140 is inserted into lumen 134 of outer shell 130, a second chamber 124 is defined in tapered distal end 136 of outer shell 130. When inner manifold 140 is so positioned, second lumen 144b of manifold 140 is in fluid communication with the second chamber 124.
As seen in FIGS. 3, 4, 6 and 7, body portion 142 of inner manifold 140 may include an annular groove 142a formed therein. As seen in FIGS. 3 and 4, annular groove 142a of body portion 142 of inner manifold 140 is configured and dimensioned to receive a complementary annular flange or rib 128 formed in body portion 132 of outer shell 130. Accordingly, annular flange 128 and annular groove 142c cooperate to fix the location of inner manifold 140 relative to outer shell 130.
In addition, as seen in FIG. 4, an adhesive or glue “G” is applied in a proximal or rear portion of lumen 134 of outer shell 130, on a proximal or rear surface of inner manifold 140, and at locations therebetween. Glue “G” functions to further secure inner manifold 140 within outer shell 130 and to create a seal between outer shell 130 and inner manifold 140 to thereby inhibit and/or prevent the escape of fluid from therebetween.
Desirably, as seen in FIGS. 2-4, hub assembly 120 includes a seal element 126 (e.g., an O-ring) disposed between body portion 132 of outer shell 130 and body portion 142 of inner manifold 140. Seal element 126 functions to reduce and/or prevent fluid from traveling between first chamber 122 and second chamber 124.
As seen in FIGS. 1-4, a first or in-flow conduit 10 is fluidly connected to first lumen 144a of inner manifold 140. Desirably, a distal end of first conduit 10 extends through housing 112 of housing assembly 110 and is frictionally inserted into first lumen 144a of inner manifold 140 of hub assembly 120.
With continued reference to FIGS. 1-4, a second or out-flow conduit 20 is fluidly connected to second lumen 144b of inner manifold 140. Desirably, a distal end of second conduit 20 extends through housing 112 of housing assembly 110 and is frictionally inserted into second lumen 144b of inner manifold 140 of hub assembly 120.
Turning now to FIGS. 1-5, needle electrode assembly 150 will be described in greater detail. Needle electrode assembly 150 includes an outer tube 152a having an exposed distal end portion 154a terminating in a sharpened distal tip 156a which is constructed so as to penetrate tissue with a minimum risk of hemorrhage from the puncture tract. Desirably, outer tube 152a is constructed form an electrically conductive material or the like. Outer tube 152a includes a proximal end portion 158a supported in housing 112, and preferably, in a distal lumen 134b formed in and extending distally from constricted passage 134a of outer shell 130, as seen in FIGS. 4 and 5. Outer tube 152a is hollow and defines a cavity 160a therein.
Desirably, the non-exposed part of outer tube 152a is surrounded by an insulating material or the like. The insulating material may be any material which is biologically acceptable and suitable for insertion into tissue. Since distal end portion 154a is exposed or non-insulated, distal end portion 154a is capable of DC or AC delivery, preferably RF delivery.
Needle electrode assembly 150 further includes an inner tube 152b disposed substantially co-axially within cavity 160a of outer tube 152a Inner tube 152b includes a distal end portion 156b (see FIGS. 6 and 7) located near distal end portion 154a of outer tube 152a and a proximal end portion 158b extending from proximal end portion 158a of outer tube 152a. Preferably, proximal end portion 158b of inner tube 152b extends through constricted passage 134a and into or through third lumen 144c of inner manifold 140. Desirably, proximal end portion 158b of inner tube 152b is in fluid communication with first cavity or chamber 122 defined between inner manifold 140 and outer shell 130, see FIGS. 2-4.
In use, cooling fluid “F” is delivered to distal tip 156a of outer tube 152a from in-flow conduit 10. In particular, cooling fluid “F” travels from in-flow conduit 10, into first chamber 122, into lumen 160b (see FIGS. 6 and 7) of inner tube 152b of needle electrode assembly 150, to distal tip 156a of outer tube 152a. Cooling fluid “F” is led away from distal tip 156a of outer tube 152a through cavity 160a, through second chamber 124, through second lumen 144b of inner manifold 140, and out through out-flow tube 20. Cooling fluid “F” may be communicated to a collecting container (not shown) or back to a source of fluid “SF” (see FIG. 1) for re-circulation. Circulation of cooling fluid “F” may be established with the use of a pump (not shown) or the like.
As seen in FIGS. 2, 3, 6 and 7, electrode ablation system 100 further includes a first electrical conduit 170 extending through housing 112 and electrically connected to outer tube 152a of needle electrode assembly 150. In particular, first electrical conduit 170 includes a distal end 170a electrically connected to outer tube 152a at a location distal of hub assembly 120 and within housing 112. First electrical conduit 170 is also electrically connected to a source of electrosurgical energy “E”. Accordingly, electrosurgical energy may be delivered from the source of electrosurgical energy, through first electrical conduit 170, to outer tube 152a.
As seen in FIGS. 2-4, 6 and 7, electrode ablation system 100 further includes a thermocouple assembly 172 operatively associated with inner tube 152b. Thermocouple assembly 172 includes a first wire 174 extending through lumen 160b of inner tube 152b. A distal end 174a of first wire 174 is desirably electrically secured to distal end portion 156b of inner tube 152b, as by, for example, soldering and the like. Desirably, first wire 174 is fabricated from constantan (i.e., a high-resistance alloy of approximately 40% nickel and 60% copper having a very low coefficient of thermal expansion). Thermocouple assembly 172 further includes a second wire 176 having a distal end 176a electrically connected to inner tube 152b, preferably a proximal end portion 158b of inner tube 152b. {What is the purpose of second wire 176?} Each of first wire 174 and second wire 176 are electrically connectable to an electrosurgical energy source “E”, an central processing unit or the like.
As seen in FIGS. 1, 2 and 7, each of electrical conduit 170, first wire 174 and second wire 176 may be contained in a single cable 180.
Turning now to FIGS. 8-12, an electrode ablation system, in accordance with another embodiment of the present disclosure, is generally designated as 200. Electrode ablation system 200 is substantially similar to ablation system 100 and will only be discussed in detail to the extent necessary to identify differences in construction and operation. Unlike electrode ablation system 100 which includes a single needle electrode assembly 150, electrode ablation system 200 includes three needle electrode assemblies 250a-250c extending distally from housing 112 of housing assembly 110. While a single and three needle electrode assemblies have been shown and described herein, it is respectfully submitted that any number of needle electrode assemblies may be provided.
As seen in FIGS. 9-12, hub assembly 220 of electrode ablation system 200 includes a hub assembly outer shell 130 and a hub assembly inner manifold 240 operatively disposed within outer shell 230.
As seen in FIGS. 9, 10 and 10A, hub assembly outer shell 230 includes a body portion 232 defining a central lumen 234 extending therethrough. Desirably, outer shell 230 includes three constricted passages 236a-236c extending through a distal end portion 230a of outer shell 230 and in fluid communication with central lumen 234. Desirably, each passage 236a-236c is sized to support and receive a proximal end of outer tube 252a of a respective needle electrode assembly 250a-250c.
As seen in FIGS. 9, 11 and 12, inner manifold 240 is configured and dimensioned for support within lumen 234 of outer shell 230. Inner manifold 240 includes a body portion 242 defining a first or inflow lumen 244a formed at least partially in a proximal end portion 242b thereof. Inner manifold 240 further includes a second or outflow lumen 244b extending entirely therethrough. Inner manifold 240 further includes a plurality of third lumens 244c formed at least partially in a distal end portion thereof 242a. Each third lumen 244c of inner manifold 240 is configured and dimensioned to receive and support a proximal end of a respective inner tube 252b of needle electrode assemblies 250a-250c therein.
As seen in FIGS. 9, 11 and 12, inner manifold 240 defines a first recess 248 formed therein such that when inner manifold 240 is inserted into lumen 234 of outer shell 230, first recess 248 defines a first cavity or chamber 222 between outer shell 230 and inner manifold 240. As can be appreciated and similar to hub assembly 120 of electrode ablation system 100, first lumen 244a and each third lumen 244c are in fluid communication with first chamber 222.
With continued reference to FIGS. 9, 11 and 12, when inner manifold 240 is inserted into lumen 234 of outer shell 230, a second chamber 224 is defined in distal end portion 236 of lumen 234 of outer shell 230. When inner manifold 240 is so positioned, second lumen 244b of manifold 240 is in fluid communication with the second chamber 224.
As seen in FIGS. 9-12, each needle electrode assembly 250a-250c of electrode ablation system 200 is substantially similar to needle electrode assembly 150 of electrode ablation system 100, and therefore reference may be made to the detailed discussion of needle electrode assembly 150 for an understanding and description of needle electrode assemblies 250a-250c.
Use of electrode ablation system 200 will now be described in detail. In use, cooling fluid “F” is delivered to a distal tip 256 of each outer tube 252a. In particular, cooling fluid travels from in-flow conduit 10, into first chamber 222, into a lumen of an inner tube (see FIGS. 6 and 7) of each needle electrode assembly 250a-250c, to a distal tip 256 of the outer tube of each needle electrode assembly 250a-250c. The cooling fluid is led away from distal tip 256 of the outer tube of each needle electrode assembly 250a-250c, through second chamber 224, through second lumen 244b of inner manifold 240, and out through out-flow tube 20.
As seen in FIGS. 11 and 12, a first wire 174 of thermocouple assembly 172 extends through lumen 160b (see FIG. 6) of at least one inner tube 252b of needle electrode assemblies 250a-250c. As mentioned above, a distal end 174a of first wire 174 is desirably electrically secured to a distal end portion of inner tube 252b, as by, for example, soldering and the like. Desirably, first wire 174 is fabricated from constantan or the like (i.e., a high-resistance alloy of approximately 40% nickel and 60% copper having a very low coefficient of thermal expansion). A second wire 176 of thermocouple assembly 172 has a distal end electrically connected to inner tube 252b
{What is the purpose of the Blue tip mounted on the distal end of the handle and through which the needle electrode assemblies extend}.
Turning now to FIGS. 13-18, electrode ablation systems 100, 200 may each include an adjustable cord strain relief member 50 operatively disposed on cable 180, in-flow conduit 10, and/or out-flow conduit 20. Strain relief member 50 is configured and dimensioned for operative engagement in an aperture 114 (see FIGS. 1 and 2) of housing 112 of handle assembly 110.
Strain relief member 50 includes a body portion 52 having a substantially hour-glass configuration. Body portion 52 may include a first substantially spherical portion 52a and a second substantially spherical portion 52b. Desirably, second portion 52b of body portion 52 is poly-axially supported (e.g., in the manner of a ball and socket joint) within a complementarily sized and shaped aperture 114.
As seen in FIGS. 14-16, an annular rib 54a may be provided on the surface of second body portion 52a for engaging the inner surface of shaped aperture 114. Strain relief member 50 may also be provided with a shield or apron 56 extending radially therefrom. Shield 56 may be disposed within an appropriately sized recess 116 formed in handle 112, as seen in FIG. 15, or may be disposed externally of handle 112, as seen in FIG. 16.
As seen in FIGS. 17 and 18, strain relief member 50 may include means for locking including a tapered portion 52c disposed between first body portion 52a and second body portion 52b, and at least one longitudinally oriented locking rib 54b projecting from tapered portion 52c. Locking rib 54b is configured and dimensioned to selectively engage complementary channels 118 formed in handle 112. In use, as strain relief member 50 is moved in a first direction (as indicated by arrow “A”), locking rib 54b disengages channels 118 to unlock strain relief member 50, and as strain relief member 50 is moved in a second direction (opposite to direction “A”), locking rib 54b engages channels 118 to lock strain relief member 50.
It is to be understood that the foregoing description is merely a disclosure of particular embodiments and is no way intended to limit the scope of the invention. Other possible modifications will be apparent to those skilled in the art and all modifications will be apparent to those in the art and all modifications are to be defined by the following claims.
Patent Application
20140180279
