Patent Application
20160338726
Ultrasonic instruments, including both hollow core and solid core instruments, are used for the safe and effective treatment of many medical conditions. Ultrasonic instruments, and particularly solid core ultrasonic instruments, are advantageous because they may be used to cut and/or coagulate tissue using energy in the form of mechanical vibrations transmitted to a surgical end effector at ultrasonic frequencies. Ultrasonic vibrations, when transmitted to organic tissue at suitable energy levels and using a suitable end effector, may be used to cut, dissect, elevate, coagulate or cauterize tissue, or to separate muscle tissue off bone. Ultrasonic instruments utilizing solid core technology are particularly advantageous because of the amount of ultrasonic energy that may be transmitted from an ultrasonic transducer, through a transmission component or waveguide, to the surgical end effector. Such instruments may be used for open or minimally invasive surgical procedures, such as endoscopic or laparoscopic surgical procedures, wherein the end effector is passed through a trocar to reach the surgical site.
Activating or exciting the single or multiple-element end effector of such instruments at ultrasonic frequencies induces longitudinal, transverse or torsional vibratory movement that generates localized heat within adjacent tissue, facilitating both cutting and coagulation. Because of the nature of ultrasonic instruments, a particular ultrasonically actuated end effector may be designed to perform numerous functions, including, for example, cutting, coagulating, scraping, or lifting tissue with or without the assistance of a clamping assembly.
Ultrasonic vibration is induced in the surgical end effector by electrically exciting a transducer, for example. The transducer may be constructed of one or more piezoelectric or magnetostrictive elements in the instrument hand piece. Vibrations generated by the transducer section are transmitted to the surgical end effector via an ultrasonic transmission component such as a waveguide extending from the transducer section to the surgical end effector. The waveguides and end effectors are most preferably designed to resonate at the same frequency as the transducer. Therefore, when an end effector is attached to a transducer the overall system frequency is the same frequency as the transducer itself.
The zero to peak amplitude of the longitudinal ultrasonic vibration at the tip, d, of the end effector behaves as a simple sinusoid at the resonant frequency as given by:
d=A sin(ωt)
where:
ω=the radian frequency which equals 2π times the cyclic frequency, f; and
A=the zero-to-peak amplitude.
The longitudinal excursion is defined as the peak-to-peak (p-t-p) amplitude, which is just twice the amplitude of the sine wave or 2 A.
Solid core ultrasonic instruments may be divided into two types, single element end effector devices and multiple-element end effector. Single element end effector devices include instruments such as blades, scalpels, hooks and/or ball coagulators. Multiple-element end effectors may include a mechanism to press tissue against an ultrasonic blade. Multiple-element end effectors comprise clamping scalpels and/or clamping coagulators or any combination of a clamping assembly with a single element end effector. Multiple-element end effectors may be employed when substantial pressure may be necessary to effectively couple ultrasonic energy to the tissue. Ultrasonic clamp coagulators, for example, may be employed for cutting and coagulating tissue, particularly loose and unsupported tissue. Multiple-element end effectors that include an ultrasonic blade in conjunction with a clamp apply a compressive or biasing force to the tissue to promote faster coagulation and cutting of the tissue.
Ultrasonic clamp coagulators provide an improved ultrasonic surgical instrument for cutting/coagulating tissue, particularly loose and unsupported tissue, wherein the ultrasonic blade is employed in conjunction with a clamp for applying a compressive or biasing force to the tissue, whereby faster coagulation and cutting of the tissue are achieved.
Ultrasonic instruments are designed and manufactured such that the maximum amplitude of the longitudinal ultrasonic vibration (i.e., the anti-node) is localized at or near the distal end of the end effector in order to maximize longitudinal excursion of the distal end. The active length of an ultrasonic instrument is generally defined as the distance from the distal end of the end effector (where ultrasonic displacement is at a maximum) to a proximal location along the end effector where ultrasonic displacement decreases below a predetermined level approaching a node (where ultrasonic displacement is at a minimum). The length segment of an end effector surrounding a node where ultrasonic displacement is below a predetermined level is defined as the nodal gap. Accordingly, the nodal gap is the length in the vicinity of the node that has insufficient displacement to generate the necessary heat for efficient and/or effective cutting and/or coagulation.
As used herein, the term “nodal gap” refers to the length segment of an end effector that has insufficient ultrasonic displacement to generate the necessary heat for efficient and/or effective cutting and/or coagulation. As used herein, the term “nodal gap region” refers to the area in the vicinity of a node and may refer to the area on or in an end effector or the area adjacent to the end effector in the vicinity of a node. As used herein, the term “nodal energy gap” refers to the condition where insufficient ultrasonic displacement to generate the necessary heat for efficient and/or effective cutting and/or coagulation is produced in the vicinity of a node.
The relatively low displacements in the vicinity of the node result in lower amounts of heat being delivered to tissue in contact with the end effector in the nodal gap region than in other regions of the end effector. Accordingly, in the nodal gap region, the tissue in contact with the blade does not get directly heated. As a result, the tissue is not effectively cut and/or coagulated, and the tissue may stick to the end effector in the nodal gap region or may simply be desiccated without being transected. It would be desirable to provide an end effector for use in an ultrasonic surgical instrument that effectively eliminates the nodal gap.
In one embodiment, an end effector for an ultrasonic surgical instrument is provided. The end effector comprises a first portion having a first specific acoustic impedance, the first portion disposed along a longitudinal axis and comprising a proximal end and a distal end; and a second portion having a second specific acoustic impedance different than the first specific acoustic impedance, the second portion disposed between the proximal end and the distal end of the first portion along the longitudinal axis.
In another embodiment, an ultrasonic blade for an ultrasonic surgical instrument is provided. The ultrasonic blade comprises a first portion having a first specific acoustic impedance, the first portion disposed along a longitudinal axis and comprising a proximal end and a distal end; and a second portion having a second specific acoustic impedance different than the first specific acoustic impedance, the second portion disposed between the proximal end and the distal end of the first portion along the longitudinal axis. The ultrasonic surgical blade comprises a body defining the longitudinal axis, the body comprising a proximal end and a distal end, wherein the distal end is movable along the longitudinal axis by ultrasonic vibrations produced by an ultrasonic transducer; a treatment region extending from the proximal end to the distal end; a top surface; and a bottom surface.
In yet another embodiment, an ultrasonic surgical instrument is provide. The ultrasonic surgical instrument comprises an end effector comprising a distal end segment, a distal insert segment, an intermediate insert segment, a proximal insert segment, and a proximal end segment, wherein the segments are disposed along a longitudinal axis having a length and configured to transmit ultrasonic vibrations along the length. The end effector comprises a first portion having a first specific acoustic impedance, the first portion disposed along a longitudinal axis and comprising a proximal end and a distal end; and a second portion having a second specific acoustic impedance different than the first specific acoustic impedance, the second portion disposed between the proximal end and the distal end of the first portion along the longitudinal axis.
The novel features of the various embodiments are set forth with particularity in the appended claims. The various embodiments, however, both as to organization and methods of operation, together with further objects and advantages thereof, may best be understood by reference to the following description, taken in conjunction with the accompanying drawings as follows.
Before explaining the various embodiments in detail, it should be noted that the embodiments are not limited in its application or use to the details of construction and arrangement of parts illustrated in the accompanying drawings and description. The illustrative embodiments may be implemented or incorporated in other embodiments, variations and modifications, and may be practiced or carried out in various ways. For example, the surgical instruments, end effector and blade configurations disclosed below are illustrative only and not meant to limit the scope or application thereof. Furthermore, unless otherwise indicated, the terms and expressions employed herein have been chosen for the purpose of describing the illustrative embodiments for the convenience of the reader and are not to limit the scope thereof.
The various embodiments relate, in general, to ultrasonic surgical end effectors for use in surgical instruments and, more particularly, to an ultrasonic surgical end effector with improved elevator, cutting and coagulation features in the nodal gap region. The various embodiments relate, in general, to ultrasonic surgical end effectors and instruments for improved bone and tissue removal, aspiration, and coagulation features. An end effector according to various embodiments is of particular benefit, among others, in procedures wherein it is desirable to remove bone and/or tissue while controlling bleeding, for example, removing muscle tissue from bone, due to its cutting and coagulation characteristics. The end effector, however, may be useful for general soft tissue cutting and coagulation. The end effector may be straight or curved, and useful for either open or laparoscopic applications. An end effector according to various embodiments may be useful in spine surgery, especially to assist in posterior access in removing muscle from bone. An end effector according to the various embodiments may reduce the user force required to remove muscle from bone and, in various embodiments, may be useful to simultaneously hemostatically seal or cauterize the tissue. Reducing the force to operate the surgical instrument may reduce user fatigue, improve precision and reduce unwanted tissue damage. A variety of different end effector configurations are disclosed which may be useful for both open and laparoscopic applications.
Examples of ultrasonic surgical instruments are disclosed in U.S. Pat. Nos. 5,322,055 and 5,954,736 and in combination with ultrasonic blades and surgical instruments disclosed in U.S. Pat. Nos. 6,309,400 B2, 6,278,218B1, 6,283,981 B1, and 6,325,811 B1, for example, are incorporated herein by reference in their entirety. These references disclose ultrasonic surgical instrument designs and blade designs where a longitudinal mode of the blade is excited. Certain embodiments will now be described to provide an overall understanding of the principles of the structure, function, manufacture, and use of the devices and methods disclosed herein. One or more examples of these embodiments are illustrated in the accompanying drawings. Those of ordinary skill in the art will understand that the devices and methods specifically described herein and illustrated in the accompanying drawings are non-limiting embodiments and that the scope of the various embodiments is defined solely by the claims. The features illustrated or described in connection with one embodiment may be combined with the features of other embodiments. Such modifications and variations are intended to be included within the scope of the claims.
In one general aspect, the various embodiments are directed to an end effector for use with an ultrasonic surgical instrument. The end effector comprises a first portion having a first specific acoustic impedance value and a second portion having a second specific acoustic impedance value. The second specific acoustic impedance value is less than the first specific acoustic impedance value.
In another general aspect, the various embodiments are directed to an end effector for use with an ultrasonic surgical instrument. The end effector comprises a distal end segment comprised of a first acoustic impedance material, a distal insert segment comprised of a second acoustic impedance material, a middle insert segment comprised of a third acoustic impedance material, a proximal insert segment comprised of a fourth acoustic impedance material, and a proximal end segment comprised of a fifth acoustic impedance material.
In yet another general aspect, the various embodiments are directed to an end effector for use with an ultrasonic surgical instrument. The end effector comprises a proximal end segment, a distal end segment, and an insert segment wherein the insert segment is located between the proximal end segment and the distal end segment. The insert segment of the end effector comprises a lossy material or a material having a specific acoustic impedance value different than the specific acoustic impedance values of the proximal end segment and the distal end segment.
In still another general aspect, the various embodiments are directed to an ultrasonic surgical blade that comprises a plurality of segments. At least one of the plurality of segments is configured to fill and/or narrow a nodal energy gap. In yet another general aspect, the various embodiments are directed to an ultrasonic surgical blade comprising a single material. The specific acoustic impedance of the blade changes along the length.
In still another general aspect, the various embodiments are directed to a surgical instrument that comprises a transducer configured to produce vibrations along a longitudinal axis at a predetermined frequency. An ultrasonic blade extends along the longitudinal axis coupled to the transducer. The blade includes a body having a proximal end and a distal end. The distal end is movable along the longitudinal axis by the vibrations produced by the transducer. A non-vibrating clamp arm assembly having a proximal end and a distal end is pivotally positioned adjacent to the body. The clamp arm assembly is pivotally moveable from an open position to a closed position. The non-vibrating clamp arm assembly comprises a proximal tissue pad segment, a distal tissue pad segment, and a tissue pad insert segment positioned between the proximal tissue pad segment and the distal tissue pad segment.
In yet another general aspect, the various embodiments are directed to surgical instrument that comprises a transducer configured to produce vibrations along a longitudinal axis as a predetermined frequency. An ultrasonic blade extends along the longitudinal axis coupled to the transducer. The blade includes a body having a proximal end and a distal end. The distal end is movable along the longitudinal axis by the vibrations produced by the transducer. An extension member comprises a proximal end and a distal end is disposed adjacent to the body. The extension member further comprises a pad positioned on the distal end of the extension member and located between the body and the distal end of the extension member.
In still another general aspect, the various embodiments are directed to surgical instrument that comprises a transducer configured to produce vibrations along a longitudinal axis at a predetermined frequency. An ultrasonic blade extends along the longitudinal axis coupled to the transducer. The blade includes a body having a proximal end and a distal end. The distal end is movable along the longitudinal axis by the vibrations produced by the transducer. A protective sheath comprising a proximal end and a distal end is disposed adjacent to the body. The protective sheath further comprises a pad positioned on the distal end of the protective sheath and located between the body and the distal end of the protective sheath.
It will be appreciated that the terms “proximal” and “distal” are used herein with reference to a clinician gripping the hand piece assembly 60. Thus, the end effector is distal with respect to the more proximal hand piece assembly 60. It will be further appreciated that, for convenience and clarity, spatial terms such as “top” and “bottom” also are used herein with respect to the clinician gripping hand piece assembly 60. However, surgical instruments are used in many orientations and positions, and these terms are not intended to be limiting and absolute.
The distal end of end-bell 20 is connected to the proximal end of transduction portion 18, and the proximal end of fore-bell 22 is connected to the distal end of transduction portion 18. Fore-bell 22 and end-bell 20 have a length determined by a number of variables, including the thickness of transduction portion 18, the density and modulus of elasticity of the material used to manufacture end-bell 20 and fore-bell 22, and the resonant frequency of the ultrasonic transducer 14. Fore-bell 22 may be tapered inwardly from its proximal end to its distal end to amplify the ultrasonic vibration amplitude as velocity transformer 28, or alternately may have no amplification. A suitable vibrational frequency range may be about 20 Hz to 120 kHz and a well-suited vibrational frequency range may be about 30-100 kHz and a suitable operational vibrational frequency may be approximately 55.5 kHz, for example.
Piezoelectric elements 32 may be fabricated from any suitable material, such as, for example, lead zirconate-titanate, lead meta-niobate, lead titanate, or other piezoelectric ceramic material. Each of positive electrodes 34, negative electrodes 36, and piezoelectric elements 32 has a bore extending through the center. Positive and negative electrodes 34 and 36 are electrically coupled to wires 38 and 40, respectively. Wires 38 and 40 are encased within cable 42 and electrically connectable to ultrasonic signal generator 12 of ultrasonic system 10.
Ultrasonic transducer 14 of acoustic assembly 24 converts the electrical signal from ultrasonic signal generator 12 into mechanical energy that results in primarily longitudinal vibratory motion of ultrasonic transducer 14 and an end effector at ultrasonic frequencies. A suitable generator is available as model number GEN04, from Ethicon Endo-Surgery, Inc., Cincinnati, Ohio. When acoustic assembly 24 is energized, a vibratory motion standing wave is generated through acoustic assembly 24. The amplitude of the vibratory motion at any point along acoustic assembly 24 may depend upon the location along acoustic assembly 24 at which the vibratory motion is measured. A minimum or zero crossing in the vibratory motion standing wave is generally referred to as a node (i.e., where motion is minimal), and a local absolute value maximum or peak in the standing wave is generally referred to as an anti-node (i.e., where motion is maximal). The distance between an anti-node and its nearest node is one-quarter wavelength (λ/4).
Wires 38 and 40 transmit an electrical signal from ultrasonic signal generator 12 to positive electrodes 34 and negative electrodes 36. Piezoelectric elements 32 are energized by the electrical signal supplied from ultrasonic signal generator 12 in response to a triggering mechanism, for example foot switch 44, to produce an acoustic standing wave in acoustic assembly 24. The electrical signal causes disturbances in piezoelectric elements 32 in the form of repeated small displacements resulting in large compression forces within the material. The repeated small displacements cause piezoelectric elements 32 to expand and contract in a continuous manner along the longitudinal axis of the voltage gradient, producing longitudinal waves of ultrasonic energy. The ultrasonic energy is transmitted through acoustic assembly 24 to an end effector via an ultrasonic transmission component such as an ultrasonic transmission waveguide.
In order for acoustic assembly 24 to deliver energy to an end effector, all components of acoustic assembly 24 must be acoustically coupled to the end effector. The distal end of ultrasonic transducer 14 may be acoustically coupled at surface 30 to the proximal end of an ultrasonic transmission waveguide by a threaded connection such as stud 48.
The components of acoustic assembly 24 are preferably acoustically tuned such that the length of any assembly is an integral number of one-half wavelengths (nλ/2), where the wavelength λ is the wavelength of a pre-selected or operating longitudinal vibration drive frequency fd of acoustic assembly 24, and where n is any positive integer. It is also contemplated that acoustic assembly 24 may incorporate any suitable arrangement of acoustic elements.
In the embodiment illustrated in
The length of blade 50 may be substantially equal to an integral multiple of one-half system wavelengths (nλ/2). Distal end 52 of blade 50 may be disposed near an anti-node in order to provide the maximum longitudinal excursion of distal end 52. When the transducer assembly is energized, distal end 52 of the blade 50 may be configured to move in the range of, for example, approximately 10 to 500 microns peak-to-peak, and preferably in the range of about 30 to 150 microns at a predetermined vibrational frequency.
Blade 50 may be coupled to ultrasonic transmission waveguide 104. Blade 50 and ultrasonic transmission guide 104 as illustrated are formed as a single unit of construction from a material suitable for transmission of ultrasonic energy such as, for example, Ti6Al4V (an alloy of titanium including aluminum and vanadium), aluminum, stainless steel, other known materials, or combinations thereof. Alternately, blade 50 may be separable (and of differing composition) from ultrasonic transmission waveguide 104, and coupled by, for example, a stud, weld, glue, quick connect, or other suitable known methods. The length of ultrasonic transmission waveguide 104 may be substantially equal to an integral number of one-half system wavelengths (nλ/2), for example. Ultrasonic transmission waveguide 104 also may be preferably fabricated from a solid core shaft constructed out of material that propagates ultrasonic energy efficiently, such as titanium alloy (e.g., Ti6Al4V) or an aluminum alloy, for example. Ultrasonic transmission waveguide 104 also may be fabricated from a hollow core shaft constructed out of similar materials. Ultrasonic transmission waveguide 104 also may be fabricated with a combination solid/hollow core shaft, for example, a solid core shaft with hollow cavities positioned at various locations along the length of the shaft.
In the embodiment illustrated in
Ultrasonic transmission waveguide 104 comprises longitudinally projecting attachment post 54 at a proximal end to couple to surface 30 of ultrasonic transmission waveguide 104 by a threaded connection such as stud 48 (
Outer sheath 106 generally includes a hub and an elongated tubular member. The tubular member is attached to the hub and has an opening extending longitudinally therethrough. Ultrasonic transmission waveguide 104 extends through the opening of the tubular member and attaches to the distal end of transducer 14. As previously discussed, outer sheath 106 attaches to ultrasonic transmission waveguide 104 by mounting pin 112 passed through mounting holes 114. Outer sheath 106 may be attached to a distal end of housing 16 or an adapter attached to housing 16 such that the rear hub of outer sheath 106 is supported by housing 106 when excessive bending torque is applied during surgery. Silicone rings isolate ultrasonic transmission waveguide 104 from outer sheath 106.
The adapter of the sheath is preferably constructed from plastic, and the tubular member is fabricated from stainless steel. Alternatively, ultrasonic transmission waveguide 104 may have polymeric material surrounding it to isolate it from outside contact.
The distal end of ultrasonic transmission waveguide 104 may be coupled to the proximal end of blade 50 by an internal threaded connection, preferably at or near an anti-node. It is contemplated that blade 50 may be attached to ultrasonic transmission waveguide 104 by any suitable means, such as a welded joint or the like. Although blade 50 may be detachable from ultrasonic transmission waveguide 104, it is also contemplated that blade 50 and ultrasonic transmission waveguide 104 may be formed as a single unitary piece.
Ultrasonic surgical instrument 100 may be sterilized by methods known in the art such as, for example, gamma radiation sterilization, ethylene oxide processes, autoclaving, soaking in sterilization liquid, or other known processes. In the illustrated embodiment, ultrasonic transmission assembly 102 includes an ultrasonic end effector, generally designated as the ultrasonic blade 50, and ultrasonic transmission waveguide 104. Blade 50 and ultrasonic transmission waveguide 104 are illustrated as a single unit construction from a material suitable for transmission of ultrasonic energy such as, for example, Ti6Al4V, aluminum, stainless steel, other known materials, and combinations thereof. Alternately, ultrasonic blade 50 may be separable (and of differing composition) from ultrasonic transmission waveguide 104, and coupled by, for example, a stud, weld, glue, quick connect, or other known methods. Ultrasonic transmission waveguide 104 may have a length substantially equal to an integral number of one-half system wavelengths (nλ/2), for example.
Clamped coagulating shears 1002 preferably includes instrument housing 1004 and elongated member 1006. Elongated member 1006 may be selectively rotated with respect to instrument housing 1004. Instrument housing 1004 includes pivoting handle portion 1028 and fixed handle portion 1029.
An indexing mechanism (not shown) is disposed within a cavity of instrument housing 1004. The indexing mechanism is preferably coupled or attached on inner tube 1014 to translate movement of pivoting handle portion 1028 to linear motion of inner tube 1014 to open and close multi-element end assembly 1008. When pivoting handle portion 1028 is moved toward fixed handle portion 1029, the indexing mechanism slide inner tube 1014 rearward to pivot multi-element end assembly 1008 into a closed position. The movement of pivoting handle portion 1028 in the opposite direction slides the indexing mechanism to displace inner tube 1014 in the opposite direction, i.e., forwardly, and hence pivot multi-element end assembly 1008 into its open position in the direction indicated by arrow 1020 as shown in
Pivoting handle portion 1028 includes thumb loop 1030. Pivot pin 1032 is disposed through a first hole of pivoting handle portion 1028 to allow pivoting as shown by arrow 1034 in
Elongated member 1006 of clamped coagulating shears 1002 extends from instrument housing 1004. Elongated member 1006 preferably includes an outer member or outer tube 1012, an inner member or inner tube 1014, and a transmission component or ultrasonic transmission waveguide 104.
The multiple-element end effector or multi-element end assembly 1008 includes clamp arm 1018, tissue pad 1036, and ultrasonic blade 1016. Clamp arm 1018 is pivotally mounted about a pivot pin (not shown) to rotate in the direction indicated by arrow 1038. Ultrasonic blade 1016 comprises tapered concave surface 1040 extending inwardly into the blade body.
As previously discussed with reference to ultrasonic system 10 (
Ultrasonic surgical instrument 100 and clamped coagulating shears 1002 may be sterilized by methods known in the art such as, for example, gamma radiation sterilization, ethylene oxide processes, autoclaving, soaking in sterilization liquid, or other known processes. In the embodiment illustrated in
In the embodiment illustrated in
The active length of an ultrasonic instrument is the length of the end effector from the distal end that achieves desired tissue effects (e.g., cutting and coagulation) during use. The active length of an ultrasonic instrument may be defined as the length/distance from the distal end of the end effector (where the ultrasonic displacement is maximum) to where ultrasonic displacement decreases below a predetermined level in the proximal direction. Outside the active length, the end effector may not deliver sufficient heat to tissue in contact with the end effector to achieve efficient and/or effective cutting and/or coagulation, for example.
In some instances, the active length is defined as the length from the distal end of the end effector to the proximal location where the ultrasonic displacement decreases to 50% of the maximum displacement. The 50% standard takes account of the ultrasonic energy generally necessary to achieve acceptable cutting and/or coagulation. However, other percentage decreases in ultrasonic displacement may be used to quantitatively define the active length (and the nodal gap). Those of ordinary skill in the art can quantitatively define the active length (and the nodal gap) according to the specific ultrasonic system involved.
The various embodiments relate, in general, to methods developed to bridge, fill or otherwise eliminate the nodal gap. The various embodiments relate, more specifically, to end effectors for use with ultrasonic surgical instruments that embody the methods to bridge, fill or otherwise eliminate the nodal gap. A first method is to narrow or close the nodal gap by modifying the composition of an end effector. This method may effectively bridge the nodal gap. A second method is to fill the nodal gap by delivering heat to tissue in the nodal gap region.
By definition, the ultrasonic displacement at a node is zero. As illustrated in
Characteristic acoustic impedance is the ratio of effective sound pressure at a point to the particle velocity at that point in a free, progressive wave in a medium. Characteristic acoustic impedance is equal to the product of the density of the medium and the speed of sound in the medium and is an intrinsic material property. The specific acoustic impedance of a system is the product of the characteristic acoustic impedance of the material comprising the system and the cross-sectional area of the system through which a wave progresses. Therefore, the displacement in the vicinity of the node, and thus the slope of the displacement-distance curve in the vicinity of the node can be increased by differences in material properties, differences in cross-sectional area, or a combination of both.
In various embodiments, proximal end segment 208 and distal end segment 210 comprise a first portion or main portion of end effector 200 having a first specific acoustic impedance value. Insert segment 212 comprises a second portion having a second specific acoustic impedance value different than the first specific acoustic impedance value. Insert segment 212 may comprise a coating on end effector 200 of a material having a second specific acoustic impedance value. The difference between the first specific acoustic impedance value and the second specific acoustic impedance value may be a consequence of differences in material properties between the first portion and the second portion, or differences in cross-sectional area between the first portion and the second portion, or both. In various embodiments, the second acoustic impedance value is less than the first specific acoustic impedance value due to the second portion comprising a material having a relatively lower characteristic acoustic impedance value and the first portion comprising a material with a relatively higher characteristic acoustic impedance value. In various embodiments, the second acoustic impedance value is less than the first specific acoustic impedance value due to the second portion having a smaller cross-sectional area than the first portion. In various embodiments, the reduction in cross-sectional area is due to internal bores or cavities that have been bored into end effector 200 (see
Distal end segment 210, proximal end segment 208 and insert segment 212 may comprise matching cross-sectional areas. Distal end segment 210 and proximal end segment 208 may comprise a first material and insert segment 212 may comprise a second material having a lower characteristic acoustic impedance value than the first material. Alternatively, distal end segment 210, proximal end segment 208 and insert segment 212 all may comprise the same material, but insert segment 212 may have a smaller cross-sectional area than distal end segment 210 and proximal end segment 208. However, the cross-sectional area of insert segment 212 can only be decreased to a value that will safely support the internal ultrasonic stresses that maximize at node 202. Decreased cross-sectional area results in decreased specific acoustic impedance, which results in increased ultrasonic displacement in the nodal gap 213, whereby the nodal gap 213 is narrowed. In various embodiments, the reduction in the cross-sectional area of insert segment 212 is due to internal bores or cavities formed in end effector 200 (see
In various embodiments, insert segment 212 is comprised of an acoustically lossy material. As used herein, a lossy material is one that dissipates as heat acoustic energy passing through the material. Generally, end effectors and other components of ultrasonic instruments are not comprised of lossy materials because it is desirable to efficiently transmit ultrasonic vibrational energy to the end effector with minimal energy dissipation. The ultrasonic displacement of the end effector converts the ultrasonic vibrational energy into heat energy during the interaction with tissue. However, due to minimal ultrasonic displacement, the end effector may not effectively or efficiently convert ultrasonic vibrational energy to heat energy in the nodal gap. Therefore, the insertion of a lossy material in an end effector at or near the nodal gap would result in the conversion of ultrasonic energy to heat in the nodal gap due to internal energy losses from the lossy material. Specifically, the lossy material allows internal ultrasonic stresses that are at a maximum at a node in the material to dissipate as heat energy. The heat losses from the lossy segment are conducted to the tissue, effectively filling the nodal energy gap in the nodal gap region.
In various embodiments, insert segment 212 comprises a lossy material and thus could potentially continue to generate heat when an ultrasonic instrument comprising an end effector 200 is operated in air or other media and not in contact with tissue. The continually generated heat could increase the localized temperature in nodal gap 213 of end effector 200. The temperature rise could be mitigated by heat transfer to neighboring regions of end effector 200. Accordingly, to mitigate the rise in temperature, in various embodiments insert segment 212 may be formed with lossy material having a cross-sectional area that is less than the cross-sectional area of distal end segment 210 and proximal end segment 208. Reducing the amount of material (i.e., decreasing the cross-sectional area of end effector 200) in nodal gap 213 decreases the specific acoustic impedance value and therefore narrows and simultaneously fills the nodal gap 213. In various embodiments, insert segment 212 comprises a material that is lossy and has a reduced cross sectional area. In various embodiments, the reduction in the cross-sectional area of insert segment 212 is due to internal bores or cavities formed in end effector 200 (see
The magnitude of the narrowing of nodal gap 213 is directly dependant on the relative values of the specific acoustic impedance values of insert segment 212 and of distal end segment 210 and proximal end segment 208. The relative steepness of the slope of the displacement-distance curve in the vicinity of node 202 can be determined by the ratio of the specific acoustic impedance value of distal end segment 210 to the specific acoustic impedance value of insert segment 212. To substantially narrow nodal gap 213 by employing materials having different characteristic acoustic impedance values, it may require that the materials have characteristic acoustic impedance values that are substantially different. This may require an end effector formed mostly of materials comprising a relatively high characteristic acoustic impedance value.
End effector 220 comprises a proximal end 224 and a distal end 226 and extends along a longitudinal axis 221. Intermediate insert segment 232 is located between proximal insert segment 234 and distal insert segment 236 along longitudinal axis 221. Proximal insert segment 234, intermediate insert segment 232 and the distal insert segment 236 are located between proximal end segment 228 and distal end segment 230 along longitudinal axis 221. Distal end segment 230 comprises a first acoustic impedance material, distal insert segment 236 comprises a second acoustic impedance material, intermediate insert segment 232 comprises a third acoustic impedance material, proximal insert segment 234 comprises a fourth acoustic impedance material, and proximal end segment 228 comprises a fifth acoustic impedance material.
In one embodiment, the second acoustic impedance material (of distal insert segment 236) and the fourth acoustic impedance material (of proximal insert segment 234) are the same material. In one embodiment, the first acoustic impedance material (of distal end segment 230) and the fifth acoustic impedance material (of proximal end segment 228) are the same material. In one embodiment, the first acoustic impedance material (of distal end segment 230), the third acoustic impedance material (of intermediate insert segment 232) and the fifth acoustic impedance material (of proximal end segment 228) are the same material. In one embodiment, the first acoustic impedance material, the third acoustic impedance material and the fifth acoustic impedance material each have greater characteristic acoustic impedance values than the second acoustic impedance material and the fourth acoustic impedance material. In one embodiment, all five acoustic impedance materials have different specific acoustic impedance values.
In one embodiment, intermediate insert segment 232 may be located at or near node 222 and positioned within the nodal gap. In another embodiment, intermediate insert segment 232 may be located within the nodal gap but offset from node 222 (not shown). In yet another embodiment, the length of insert segment 232 along longitudinal axis 221 may correspond to the length of the nodal gap (not shown). In still another embodiment, intermediate insert segment 232 may be offset from node 222 and completely or partially outside the nodal gap (not shown). In yet another embodiment, proximal insert segment 234, intermediate insert segment 232 and distal insert segment 236 may be located within the nodal gap. In still another embodiment, proximal insert segment 234, intermediate insert segment 232 and distal insert segment 236 may be located partially or completely outside the nodal gap.
In various embodiments, the second acoustic impedance material (or distal insert segment 276) and the fourth acoustic impedance material (of proximal insert segment 274) are different materials.
In various embodiments, the first acoustic impedance material (of the distal end segment 290) and the fifth acoustic impedance material (of proximal end segment 288) are different materials.
In various embodiments, the third acoustic impedance material (of intermediate insert segment 252) may have a greater acoustic impedance value than the first acoustic impedance material (of distal end segment 250) and the fifth acoustic impedance material (of proximal end segment 248). The second acoustic impedance material (of distal insert segment 256) and the fourth acoustic impedance material (of proximal insert segment 254) may have lower acoustic impedance values than the first acoustic impedance material and the fifth acoustic impedance material.
In one embodiment, intermediate insert segment 252 may be located at or near node 242 and positioned within the nodal gap. In another embodiment, intermediate insert segment 252 may be located within the nodal gap but offset from node 242 (not shown). In yet another embodiment, the length of insert segment 252 along longitudinal axis 241 may correspond to the length of the nodal gap (not shown). In still another embodiment, intermediate insert segment 252 may be offset from node 242 and completely or partially outside the nodal gap (not shown). In yet another embodiment, proximal insert segment 254, intermediate insert segment 252 and distal insert segment 256 may be located within the nodal gap. In still another embodiment, proximal insert segment 254, intermediate insert segment 252 and distal insert segment 256 may be located partially or completely outside the nodal gap.
The insert segments described in conjunction with
The characteristic acoustic impedances of three common metals in surgical instruments are substantially different.
Stainless Steel (SS): 40*106 rayls
Titanium (TI): 22*106 rayls
Aluminum (AL): 14*106 rayls
TABLE 1 presents the results of a mathematical model based on a simple end effector design using the materials listed above and various configurations for bridging and/or filling the nodal gap. The end effectors comprise a main portion or first portion comprising a proximal end segment and a distal end segment, and further comprise a second portion comprising an insert segment. The length and position of the insert segment may be selected so that the insert segment is located at the node and the slopes of the displacement-distance curves intersect at a predetermined displacement value as illustrated in
The most substantial reduction in the nodal gap is seen with the stainless steel end effector comprising aluminum inserts. The stainless steel end effector with no insert has a nodal gap of 0.601 inches measured between the 50% ultrasonic displacement amplitude points. The stainless steel end effector comprising an aluminum insert segment having a cross-sectional area matching the cross-sectional area of the stainless steel portion has a nodal gap narrowed to 0.221 inches measured between the 50% ultrasonic displacement amplitude points. The stainless steel end effector comprising an aluminum insert segment having a cross-sectional area half the cross-sectional area of the stainless steel portion has a nodal gap narrowed to 0.134 inches measured between the 50% ultrasonic displacement amplitude points. This is a 78 percent reduction in the length of the nodal gap.
Those of ordinary skill in the art will recognize that the particular configuration of an end effector (i.e., the dimensions, shape, and exact materials of construction) is determined, in part, by the particular characteristics of the ultrasonic instrument in which the end effector is to be used. However, the end effectors described herein may include, but are not limited to, ultrasonic surgical blade designs such as those described in conjunction with reference to
The end effectors described herein may be manufactured using any known methods of machining or other suitable fabrication methods. For example, the TI-TI-TI or AL-AL-AL end effectors in Table 1 can readily be manufactured using standard lathe techniques and/or electrical discharge machining (EDM) techniques. Those of ordinary skill in the art will appreciate the details regarding the particular machining techniques employed, for example, the formation of recast layers during EDM that typically require buffing to prevent the metal from embrittling. In addition, end effectors comprising insert segments of dissimilar materials compared to the material of the main portion (e.g., the SS-AL-SS and TI-AL-TI configurations in Table 1) may be manufactured by any suitable methods, such as, for example, laser welding.
Those skilled in the art will also recognize that the shape and configuration of a reduced-area segment will be governed, in part, by the particular characteristics of the end effector and the ultrasonic system employed. It is also recognized that the term “insert segment” has been used herein to describe, among other things, a portion of an end effector that has a reduced cross-sectional area with respect to the main portion of the end effector. For example, “insert segment” may refer to a region of an end effector comprising an internal cavity or bore. The term “insert segment” has also been used herein to describe regions or portions of end effectors comprising coatings. The term “insert segment” is intended to describe these regions or portions of an end effector in a general manner and is not limiting with regard to the method by which the region or portion is manufactured.
Various embodiments have been described for bridging, filling or otherwise eliminating the nodal gap (e.g., narrowing the length of the nodal gap or filling the nodal energy gap with heat) by manipulating the materials and/or geometry of an end effector. Additional embodiments relate to filling the nodal energy gap with heat generated from structures interacting with an end effector. In these embodiments, the end effector may be an ultrasonic surgical blade that conducts heat generated due to frictional interaction with insert segments located on clamp arms and/or pads located on additional components of ultrasonic instruments. The insert segments and/or pads are positioned such that the frictionally-generated heat is conducted into the nodal gap region of the ultrasonic blade, effectively filling the nodal energy gap.
The various embodiments of ultrasonic surgical blade 452 illustrated in
Those of ordinary skill in the art will recognize that tissue pad insert segment 468 may be dimensioned and positioned in the tissue pad of clamp arm assembly 460 in order to achieve the desired frictional heating effects. For example, in various embodiments, tissue pad insert segment 468 may be raised relative to the nominal height of the tissue pad (comprising proximal tissue pad segment 466 and distal tissue pad segment 470) and may be offset from node 474 when clamp arm assembly 460 is in a closed position. In various embodiments, tissue pad insert segment 468 may be flush with the top surface of the tissue pad and centered on node 474. In other embodiments, tissue pad insert segment 468 may be raised relative to the nominal height of the tissue pad and centered on node 474. In still other embodiments, tissue pad insert segment 468 may be flush with the top surface of the tissue pad and may be offset from node 474. Tissue pad insert segment 468 can be dimensioned (i.e., have length, width and thickness) in order to achieve desired fractional heating effects. The flexibility in the positioning and dimensioning of tissue pad insert segment 468 allows the profile of the additional heat frictionally-generated along blade 452 to be designed for a given application.
Tissue pad insert segment 468 can be manufactured from any material suitable for frictionally-generating heat when forced against ultrasonic surgical blade 452. Exemplary materials for tissue pad insert segment 468 include polymeric materials with high melting temperatures and high effective coefficients of friction. Polyimide is one such exemplary material. Furthermore, tissue pad insert segment 468 may be a raised region of the tissue pad where insert segment 468, proximal tissue pad segment 466 and distal tissue pad segment 470 are all the same material and manufactured as one continuous component in a single unit of construction.
Insert segment 658 may be positioned between proximal tissue pad segment 656 and distal tissue pad segment 660 on clamp arm 653 at a location that corresponds to a nodal gap region of blade 654 when clamp arm assembly 652 is in a closed position. In one embodiment, insert segment 658 may be located at or near node 662 and positioned within the nodal gap when clamp arm assembly 652 is in a closed position. In another embodiment, insert segment 658 may be located within the nodal gap but offset from node 662 (not shown). In yet another embodiment, the length of insert segment 658 along clamp arm 653 may correspond to the length of the nodal gap (not shown). In still another embodiment, insert segment 658 may be offset from node 662 and completely or partially outside the nodal gap (not shown).
In various embodiments, the clamp arm may comprise a T-shaped slot for accepting a T-shaped flange of a proximal tissue pad segment, a distal tissue pad segment and a tissue pad insert segment. In various embodiments, a single unitary tissue pad assembly may comprise the proximal tissue pad segment, the distal tissue pad segment and the tissue pad insert segment, and further comprise a T-shaped flange for reception in a T-shaped slot in the clamp arm assembly. Additional configurations including dove tailed-shaped slots and wedge-shaped flanges are contemplated. As would be appreciated by those skilled in the art, flanges and corresponding slots have alternative shapes and sizes to removably secure the tissue pad segments to the clamp arm.
A method for replacing the proximal tissue pad segment, the distal tissue pad segment and/or the tissue pad insert segment include one or more of the steps of: a) disengaging the clamp arm assembly from the ultrasonic surgical instrument; b) removing at least one of the tissue pad segments from the clamp arm; c) inserting at least one new or reconditioned tissue pad segment into the clamp arm; and d) engaging the clamp arm assembly with the ultrasonic surgical instrument. In this removal and replacement process, the new or reconditioned proximal tissue pad segment, distal tissue pad segment and tissue pad insert segment may be multiple separate segments or of unitary construction.
Another method for replacing the proximal tissue pad segment, the distal tissue pad segment and/or the tissue pad insert segment include one or more of the steps of: a) opening flanges on the clamp arm; b) removing at least one of the tissue pad segments from the clamp arm; c) inserting at least one new or reconditioned tissue pad segment into the clamp arm; and d) closing flanges on the clamp arm. In this removal and replacement process, the new or reconditioned proximal tissue pad segment, distal tissue pad segment and tissue pad insert segment may be multiple separate segments or of unitary construction.
Ultrasonic surgical blade 502 is positioned such that a length equal to approximately three-quarters (3λ/4) of a wavelength of the ultrasonic vibrational wave is exposed. Clamp arm assembly 510 is pivotally moveable from an open position to a closed position. Clamp arm assembly 510 may pivot along an arc in a manner analogous to clamp arm 460 discussed in conjunction with
In other embodiments, extension member 520 may be a component separate from outer tube 518. For example, extension member 520 may be a protective sheath comprising proximal end 526 and distal end 528 and disposed adjacent to blade body 504. Pad 522 may be positioned on protective sheath 520 toward distal end 528 and located between body 504 and distal end 528 of protective sheath 520. In various embodiments, protective sheath 520 may be fixedly attached to ultrasonic surgical instrument 500. In other embodiments, protective sheath 520 may be slideably engaged with ultrasonic surgical instrument 500. In various embodiments, protective sheath 520 may be deployable by advancing protective sheath 520 along longitudinal axis 524 toward distal end 508 of blade 502. Protective sheath 520 may be retractable toward a proximal end along longitudinal axis 524.
Pad 522 can be manufactured from any known material suitable for frictionally-generating heat when forced against ultrasonic surgical blade 502. Exemplary materials for pad 522 include polymeric materials with high melting temperatures and high effective coefficients of friction. Polyimide is one such exemplary material. Furthermore, pad 522 may be a raised region of extension member 520. In various embodiments, extension member 520 and pad 522 may be manufactured as a continuous component of the same material in a single unit of construction.
Additional advantages of pad 522 include that pad 522 provides mechanical support to ultrasonic surgical blade 502 having increases exposed length. In this regard, pad 522 functions in a dual role; generating heat to fill the nodal energy gap and supporting the increased mechanical load on deflected blade 502 when engaged with activated blade body 504 when clamp arm assembly 510 is in a closed position (see
In various embodiments, an end effector may comprise a single unit of solid construction comprising a single material and having no cavities, where the specific acoustic impedance of the end effector changes along its length, either gradually or abruptly. In such embodiments, the desired specific acoustic impedance profile along the length of the end effector can be formed by cold working the end effector.
In various embodiments, the methods and techniques for bridging and filling the nodal gap are combined in ultrasonic surgical instruments. For example, in various embodiments an ultrasonic surgical instrument may have both a tissue pad insert segment positioned on a clamp arm assembly and a pad positioned on an extension member. In other embodiments, an ultrasonic surgical instrument may have a tissue pad insert segment on a clamp arm assembly and an end effector having an insert segment having a relatively low specific acoustic impedance value and/or comprising a lossy material or a high friction material (or coatings of such materials on the end effector). In still other embodiments, an ultrasonic surgical instrument may have a pad positioned on an extension member and an end effector having an insert segment having a relatively low specific acoustic impedance value and/or comprising a lossy material or high friction material (or coatings of such materials on the end effector). It is also contemplated that an ultrasonic surgical instrument may have a tissue pad insert segment positioned on a clamp arm assembly, a pad positioned on an extension member, and an end effector having an insert segment having a relatively low specific acoustic impedance value and/or comprising a lossy material or high friction material (or coatings of such materials on the end effector) (
The devices disclosed herein can be designed to be disposed of after a single use, or they can be designed to be used multiple times. In either case, however, the devices can be reconditioned for reuse after at least one use. Reconditioning can include any combination of the steps of disassembly of the device, followed by cleaning or replacement of particular pieces, and subsequent reassembly. In particular, the device can be disassembled, and any number of the particular pieces or parts of the device can be selectively replaced or removed in any combination. Upon cleaning and/or replacement of particular parts, the device can be reassembled for subsequent use either at a reconditioning facility, or by a surgical team immediately prior to a surgical procedure. Those skilled in the art will appreciate that reconditioning of a device can utilize a variety of techniques for disassembly, cleaning/replacement, and reassembly. Use of such techniques, and the resulting reconditioned device, are all within the scope of the present application.
Preferably, the various embodiments described herein will be processed before surgery. First, a new or used instrument is obtained and if necessary cleaned. The instrument can then be sterilized. In one sterilization technique, the instrument is placed in a closed and sealed container, such as a plastic or TYVEK® bag. The container and instrument are then placed in a field of radiation that can penetrate the container, such as gamma radiation, x-rays, or high-energy electrons. The radiation kills bacteria on the instrument and in the container. The sterilized instrument can then be stored in the sterile container. The sealed container keeps the instrument sterile until it is opened in the medical facility.
It is preferred that the device is sterilized. This can be done by any number of ways known to those skilled in the art including beta or gamma radiation, ethylene oxide, steam.
Although various embodiments have been described herein, many modifications and variations to those embodiments may be implemented. For example, different types of end effectors may be employed. Also, where materials are disclosed for certain components, other materials may be used. The foregoing description and following claims are intended to cover all such modification and variations.
Any patent, publication, or other disclosure material, in whole or in part, that is said to be incorporated by reference herein is incorporated herein only to the extent that the incorporated materials does not conflict with existing definitions, statements, or other disclosure material set forth in this disclosure. As such, and to the extent necessary, the disclosure as explicitly set forth herein supersedes any conflicting material incorporated herein by reference. Any material, or portion thereof, that is said to be incorporated by reference herein, but which conflicts with existing definitions, statements, or other disclosure material set forth herein will only be incorporated to the extent that no conflict arises between that incorporated material and the existing disclosure material.
This application is a continuation application claiming priority under 35 U.S.C. §120 to U.S. patent application Ser. No. 13/849,627 entitled ULTRASONIC END EFFECTORS WITH INCREASED ACTIVE LENGTH, filed Mar. 25, 2013, now U.S. Patent Application Publication No. 2013/0226207, which is a divisional application claiming priority under U.S.C. §121 to U.S. patent application Ser. No. 11/881,662 entitled ULTRASONIC END EFFECTORS WITH INCREASED ACTIVE LENGTH, filed Jul. 27, 2007, now U.S. Pat. No. 8,523,889, the entire disclosures of which are incorporated by reference herein.
| Number | Date | Country | |
|---|---|---|---|
| Parent | 11881662 | Jul 2007 | US |
| Child | 13849627 | US |
| Number | Date | Country | |
|---|---|---|---|
| Parent | 13849627 | Mar 2013 | US |
| Child | 15227587 | US |
