CROSS-REFERENCE TO RELATED APPLICATIONS

This application claims the benefit of, and priority to, U.S. Provisional Application No. 62/301,907, filed March 1, 2016, the content of which is hereby incorporated by reference herein in its entirety.

FIELD

The present disclosure relates generally to medical devices, and, more particularly, to an ablation device configured to achieve simultaneous resection and coagulation, or hemostatic sealing, of a tissue.

BACKGROUND

There are many medical procedures in which tissue is cut or carved away for diagnostic or therapeutic reasons. For example, during hepatic transection, one or more lobes of a liver containing abnormal tissue, such as malignant tissue or fibrous tissue caused by cirrhosis, are cut away. There are a number of available electrosurgical devices for carrying out resection of tissue. However, regardless of the electrosurgical device used, extensive bleeding can occur, which can obstruct the surgeon's view and lead to dangerous blood loss levels, requiring transfusion of blood, which increases the complexity, time, and expense of the resection procedure.

In order to prevent extensive bleeding or accumulation of fluid, hemostatic mechanisms, such as blood inflow occlusion, coagulants, as well as energy coagulation (e.g., electrosurgical coagulation or argon-beam coagulation) can be used. Unlike resection, which involves application of highly intense and localized heating sufficient enough to break intercellular bonds, energy coagulation of tissue involves the application of low level current that denatures cells to a sufficient depth without breaking intercellular bonds, i.e., without cutting the tissue.

Because of their natural coagulation capability, ease of use, and ubiquity, electrosurgical modalities may be used to resect tissue. However, when electrosurgically resecting tissue, care must be taken to prevent the heat generated by the electrode from charring the tissue, which generates an undesirable odor, results in tissue becoming stuck on the electrosurgical probe, and most importantly, increases tissue resistance, thereby reducing the efficiency of the procedure. Current electrosurgical modalities, however, may generally lack the ability to be selectively and efficiently operated in a resecting mode and a coagulation mode, or both, so as to effectively resect tissue, while preventing tissue charring and maintaining hemostasis at the treatment site.

SUMMARY

The present invention relates to an ablation device configured to achieve both resection and coagulation of tissue. The ablation device can be used during an electrosurgical resection procedure to both resect tissue and further selectively coagulate surrounding tissue in the resection site so as to prevent or stop fluid accumulation (e.g., blood from vessel(s)) as a result of the resection of tissue. Accordingly, the ablation device of the present invention may be particularly useful in procedures involving the removal of unhealthy, or otherwise undesired, tissue from any part of the body in which resection may be beneficial. Thus, tumors, both benign and malignant, may be removed via surgical intervention with an ablation device described herein.

The tissue ablation device of the present invention generally includes a probe including an elongated shaft configured as a handle and adapted for manual manipulation and a

nonconductive distal portion, or distal tip, coupled to the shaft. The nonconductive distal tip includes an electrode array configured to operate in a coagulation mode. The electrode array is composed of a plurality of conductive wires, wherein one or more of the wires may receive energy in the form of electrical current from a source (e.g., RF generator) and emit RF energy in response, resulting in coagulation of tissue in contact therewith. The nonconductive distal tip further includes a single cutting, or resecting, conductive wire. The cutting wire is configured to receive energy in the form of electrical current from the source (e.g., RF generator) and emit RF energy in response, thereby resulting in the resection of a tissue. The device may include a device controller, for example, configured to selectively control the supply of electrical current to the coagulation electrode array and the cutting wire, thereby allowing the device to operate in a cutting mode, a coagulation mode, or both such that the device can simultaneously resect and coagulate tissue at the target site.

The ability of the device to provide both resection and coagulation of tissue is dependent, not only on the nature of the electrical energy delivered to the conductive wires of the electrode array or the single cutting wire, but also on the geometry of the conductive wires along the nonconductive tip. The smaller the surface area of an electrode in proximity to the tissue, the greater the current density of an electrical arc generated by the electrode, and thus the more intense the thermal effect, thereby cutting the tissue. In contrast, the greater the surface area of the electrode in proximity to the tissue, the less the current density of the electrical arc generated by the electrode, thereby coagulating the tissue.

As such, the distal tip has a specific geometry that plays an important role in determining the current density (i.e., the amount of current distributed over an area) of energy emitted by the electrode array and cutting wire. In particular, the distal tip includes at least two opposing sides or faces sharing a common distal-facing edge. Each of the opposing sides of the distal tip includes a generally planar surface providing a relatively large surface area upon which the electrode array is positioned. The distal-facing edge has a leading end and a trailing end, wherein the leading end extends further from the distal tip than the trailing end. The cutting wire is positioned along, and generally follows the length of, the distal-facing edge. Accordingly, a portion of the cutting wire adjacent to the leading end of the edge has a relatively small surface area (when compared to the electrode array surface area) forming an energy focusing portion. Thus, because of the arrangement of the cutting wire along the distal-facing edge, including the energy-focusing portion at the leading end of the edge, the cutting wire can be placed in proximity to the tissue and cut the tissue. In contrast, positioning of the coagulation electrode array on the relatively large surface area of the planar sides or faces of the distal tip allows the electrode array to coagulate tissue.

The ablation device of the present invention is further configured to provide a conductive fluid, such as saline, to the distal tip, which may include one or more ports (e.g., ports through which conductive wires are threaded, additional fluid ports, etc.). The saline weeping through the ports and to an outer surface of the distal tip is able to carry electrical current from electrode array and/or the cutting wire, such that energy is transmitted from the electrode array, or cutting wire, to the tissue by way of the saline weeping from the ports, thereby creating a virtual electrode. Accordingly, upon the fluid weeping through the ports, a pool or thin film of fluid is formed on the exterior surface of the distal tip and is configured to resect and/or coagulate surrounding tissue via the electrical current carried from the electrode array. BRIEF DESCRIPTION OF THE DRAWINGS

Features and advantages of the claimed subject matter will be apparent from the following detailed description of embodiments consistent therewith, which description should be considered with reference to the accompanying drawings, wherein:

FIG. 1 is a schematic illustration of an ablation system consistent with the present disclosure;

FIG. 2 is a perspective view of one embodiment of an ablation device compatible with the ablation system of FIG. 1;

FIGS. 3A, 3B, 3C, and 3D are perspective and side views of the nonconductive distal tip of the ablation device of FIG. 2 in greater detail;

FIG. 4 is a perspective view of another embodiment of an ablation device compatible with the ablation system of FIG. 1; and

FIGS. 5 A and 5B are perspective and side views of the nonconductive distal tip of the ablation device of FIG. 4 in greater detail.

For a thorough understanding of the present disclosure, reference should be made to the following detailed description, including the appended claims, in connection with the above- described drawings. Although the present disclosure is described in connection with exemplary embodiments, the disclosure is not intended to be limited to the specific forms set forth herein. It is understood that various omissions and substitutions of equivalents are contemplated as circumstances may suggest or render expedient.

DETAILED DESCRIPTION

By way of overview, the present disclosure is generally directed to a tissue ablation system including an ablation device to be delivered to a target site and achieve both resection and coagulation of tissue. The ablation device can be used during an electrosurgical resection procedure to both resect tissue and further selectively coagulate surrounding tissue in the resection site so as to prevent or stop fluid accumulation (e.g., blood from vessel(s)) as a result of the resection of tissue. Accordingly, the ablation device of the present invention may be particularly useful in procedures involving the removal of unhealthy, or otherwise undesired, tissue from any part of the body in which resection may be beneficial. Thus, tumors, both benign and malignant, may be removed via surgical intervention with an ablation device described herein.

The tissue ablation device of the present invention generally includes a probe including an elongated shaft configured as a handle and adapted for manual manipulation and a

nonconductive distal portion (also referred to herein as "distal tip") coupled to the shaft. The nonconductive distal tip includes an electrode array configured to operate in a coagulation mode. The electrode array is composed of a plurality of conductive wires, wherein one or more of the wires may receive energy in the form of electrical current from a source (e.g., RF generator) and emit RF energy in response, resulting in coagulation of tissue in contact therewith. The nonconductive distal tip further includes a single cutting, or resecting, conductive wire. The cutting wire is configured to receive energy in the form of electrical current from the source (e.g., RF generator) and emit RF energy in response, thereby resulting in the resection of a tissue. The device may include a device controller, for example, configured to selectively control the supply of electrical current to the coagulation electrode array and the cutting wire, thereby allowing the device to operate in a cutting mode, a coagulation mode, or both such that the device can simultaneously resect and coagulate tissue at the target site.

The ability of the device to provide both resection and coagulation of tissue is dependent, not only on the nature of the electrical energy delivered to the conductive wires of the electrode array or the single cutting wire, but also on the geometry of the conductive wires along the nonconductive tip. The smaller the surface area of an electrode in proximity to the tissue, the greater the current density of an electrical arc generated by the electrode, and thus the more intense the thermal effect, thereby cutting the tissue. In contrast, the greater the surface area of the electrode in proximity to the tissue, the less the current density of the electrical arc generated by the electrode, thereby coagulating the tissue.

As such, the distal tip has a specific geometry that plays an important role in determining the current density (i.e., the amount of current distributed over an area) of energy emitted by the electrode array and cutting wire. In particular, the distal tip includes at least two opposing sides or faces sharing a common distal-facing edge. Each of the opposing sides of the distal tip includes a generally planar surface providing a relatively large surface area upon which the electrode array is positioned. The distal-facing edge has a leading end and a trailing end, wherein the leading end extends further from the distal tip than the trailing end. The cutting wire is positioned along, and generally follows the length of, the distal-facing edge. Accordingly, a portion of the cutting wire adjacent to the leading end of the edge has a relatively small surface area (when compared to the electrode array surface area) forming an energy focusing portion. Thus, because of the arrangement of the cutting wire along the distal-facing edge, including the energy-focusing portion at the leading end of the edge, the cutting wire can be placed in proximity to the tissue and cut the tissue. In contrast, positioning of the coagulation electrode array on the relatively large surface area of the planar sides or faces of the distal tip allows the electrode array to coagulate tissue.

The ablation device of the present invention is further configured to provide a conductive fluid, such as saline, to the distal tip, which may include one or more ports (e.g., ports through which conductive wires are threaded, additional fluid ports, etc.). The saline weeping through the ports and to an outer surface of the distal tip is able to carry electrical current from electrode array and/or the cutting wire, such that energy is transmitted from the electrode array, or cutting wire, to the tissue by way of the saline weeping from the ports, thereby creating a virtual electrode. Accordingly, upon the fluid weeping through the ports, a pool or thin film of fluid is formed on the exterior surface of the distal tip and is configured to resect and/or coagulate surrounding tissue via the electrical current carried from the electrode array.

The devices and systems of the present disclosure can help to ensure that target tissue can be removed via resection while further providing a coagulation capability for addressing any fluid accumulation issues or extensive bleeding as a result of the resection, thereby improving a surgeon's ability to carry out the resection procedure. For example, when a blood vessel is encountered, RF energy can be applied via the electrode array operating in the coagulation mode, so as to shrink the collagen in the blood vessel, thereby closing the blood lumen and achieving hemostasis. In some instances, the cutting wire may be used to hemostatically seal smaller blood vessels (e.g., less than 3 mm in diameter). For example, hemostasis may be achieved via the cutting wire, for example, by utilizing the energy-focusing point in contact with the blood vessel. During or after resection of the tissue, RF energy can be applied to any "bleeders" (i.e., vessels from which blood flows or oozes) to provide complete hemostasis for the resected organ.

FIG. 1 is a schematic illustration of an ablation system 10 for providing improved resection and coagulation of tissue during a resection procedure in a patient 12. The ablation system 10 generally includes an ablation device 14, which includes a probe having a distal tip or portion 16 and an elongated catheter shaft 17 to which the distal tip 16 is connected. The catheter shaft 17 may generally include a nonconductive elongated member including a fluid delivery lumen. The ablation device 14 may further be coupled to a device controller 18 and an ablation generator 20 over an electrical connection (electrical line 32 shown in FIG. 2), and an irrigation pump or drip 22 over a fluid connection (fluid line 36 shown in FIG. 2).

The device controller 18 may include hardware/software configured to provide a user with the ability to control electrical output to the ablation device 14 in a manner so as to control the resection or coagulation of tissue. For example, as will be described in greater detail herein, the ablation device may be configured to operate in a "cutting mode", a "coagulation mode", or both modes simultaneously depending on input from a user. In some embodiments, the ablation device may be configured to operate in other modes, in addition to the "cutting" and

"coagulation" modes. For example, in some embodiments, the device may be configured to operate in a "measurement mode" in which data can be collected, such as certain measurements (e.g., temperature, conductivity (impedance), etc.) can be taken and further used by the controller 18 so as to provide an estimation of the state of tissue during a electrosurgical resection procedure, as will be described in greater detail herein.

Further still, the device controller 18 may include a custom ablation shaping (CAS) system configured to provide a user with custom ablation shaping, which includes the creation of custom, user-defined ablation geometries or profiles from the ablation device 14. The CAS system may further be configured to provide ablation status mapping based on real-time data collection (e.g., measurements) collected by the device, wherein such a CAS system is described in co-pending U.S. Application No. 15/419,269, filed January 30, 2017, the entirety of which is incorporated by reference herein. In some cases, the device controller 18 may be housed within the ablation device 14. The ablation generator 20 may also connected to a return electrode that is attached to the skin of the patient 12.

As will be described in greater detail herein, during a resection procedure, the ablation generator 20 may generally provide RF energy (e.g., electrical energy in the radiofrequency (RF) range (e.g., 350-800 kHz)) to an electrode array of the ablation device 14, as controlled by the device controller 18. At the same time, saline may also be released from the distal tip 16. The RF energy travels through the blood and tissue of the patient 12 to the return electrode and, in the process, ablates the region(s) of tissues adjacent to portions of the electrode array that have been activated.

FIG. 2 is a perspective view of ablation device 14. As previously described, the ablation device 14 includes a probe 17 including an elongated shaft configured as a handle and adapted for manual manipulation. Accordingly, as shown in FIG. 2, the probe 17 is in the form of a handle having a distal end 24 to which the distal tip 16 is coupled and a proximal end 26. As shown, the proximal end 26 of the probe 17 may be coupled to the ablation generator 20 and/or irrigation pump 22 via an electrical line 32 and a fluid line 36, respectively. Each of the electrical line 32 and fluid line 36 may include an adaptor end 34, 38 configured to couple the associated lines with a respective interface on the ablation generator 20 and irrigation pump 22.

In some examples, the ablation device 14 may further include a user interface 28 serving as the device controller 18 and in electrical communication with the ablation generator 20 and the ablation device 14. The user interface 28 may include, for example, selectable buttons 30a, 30b for providing a user with one or more operating modes with respect to controlling the resection and coagulation output of the device 14, as will be described in greater detail herein. For example, the selectable buttons 30a, 30b allow a user to control electrical output to the ablation device 14 in a manner so as to control the resection or coagulation of tissue, such that selection of button 30a results in a cutting mode (e.g., energizing cutting wire) and selection of button 30b results in a coagulation mode (energizing electrode array).

The nonconductive distal tip includes an electrode array 40 configured to operate in a coagulation mode and a single and separate cutting, or resecting, conductive wire 42 configured to operate in a cutting mode. The electrode array 40 is generally composed of a plurality of conductive wires (shown as four separate conductive wires), wherein one or more of the wires may receive energy in the form of electrical current from the RF generator 20 and emit RF energy in response, resulting in coagulation of tissue in contact therewith. The cutting wire 42 is configured to receive energy in the form of electrical current from the source (e.g., RF generator) and emit RF energy in response, thereby resulting in the resection of a tissue. As previously described, a user need only provide input (e.g., select one of buttons 30a, 30b) so as to operate the ablation device 14 in the cutting mode, coagulation mode, or both, in which a supply of electrical current is provided to the cutting wire 42 or one or more of the conductive wires of the coagulation electrode array 40, or both. The distal tip 16 may include a non-conductive material (e.g., a polyamide) as a layer on at least a portion of an internal surface, an external surface, or both an external and internal surface. In other examples, the tip 16 may be formed from a non-conductive material.

Additionally or alternatively, the tip 16 material can include an elastomeric material or a shape memory material. In some embodiments, the tip 16 may be rigid, and thus may maintain a default shape.

The distal tip 16 includes a specific geometry or shape that plays an important role in determining the current density (i.e., the amount of current distributed over an area) of energy emitted by the electrode array 40 and cutting wire 42. The ability of the device 14 to provide both resection and coagulation of tissue is dependent, not only on the nature of the electrical energy delivered to the conductive wires of the electrode array 40 or the single cutting wire 42, but also on the geometry of the conductive wires along the tip 16. The smaller the surface area of an electrode in proximity to the tissue, the greater the current density of an electrical arc generated by the electrode, and thus the more intense the thermal effect, thereby cutting the tissue. In contrast, the greater the surface area of the electrode in proximity to the tissue, the less the current density of the electrical arc generated by the electrode, thereby coagulating the tissue.

FIGS. 3A, 3B, 3C, and 3D are various views of the nonconductive distal tip 16 of the ablation device 14 in greater detail. FIG. 3A shows a perspective view of the distal tip 16. As shown, the distal tip 16 generally includes at least two opposing sides or faces 44 (44a, 44b in FIG. 3C) sharing a common distal-facing edge 46. Each of the opposing sides 44 of the distal tip 16 includes a generally planar surface providing a relatively large surface area upon which the electrode array 40 is positioned. As illustrated in the figures, the electrode array includes at least four conductive wires, thus the electrode array 40 may include a plurality of conductive wires. It should be noted, however, that the electrode array 40 may include any number of conductive wires and is not limited to four or more. The plurality of conductive wires extend within the distal tip 16, through one or more ports 45 provided on the side 44 and along an external surface of the side 44. The conductive wires generally extend along the longitudinal length of the side 44 (in a vertical direction) and are spaced apart from each other. The conductive wires transmit RF energy from the ablation generator and can be formed of any suitable conductive material (e.g., a metal such as stainless steel, nitinol, or aluminum). In some examples, the conductive wires are metal wires. It should be noted that other electrode array configurations are contemplated herein. For example, although shown to be arranged in a vertical fashion, the conductive wires of the electrode array 40 may be arranged in a different configuration. For example, in one

embodiment, the conductive wires may be positioned substantially parallel to the distal-facing edge 46 or may be oriented at an angle relative to the distal-facing edge 46.

In some embodiments, one or more of the conductive wires can be electrically isolated from one or more of the remaining conductive wires, such that the electrical isolation enables various operation modes for the ablation device 14. For example, ablation energy may be supplied to one or more conductive wires in a bipolar mode, a unipolar mode, or a combination bipolar and unipolar mode. In the unipolar mode, ablation energy is delivered between one or more conductive wires of the electrode array 40 and a return electrode, for example. In bipolar mode, energy is delivered between at least two of the conductive wires, while at least one conductive wire remains neutral. In other words, at least, one conductive wire functions as a grounded conductive wire (e.g., electrode) by not delivering energy over at least one conductive wire.

Since each conductive wire in the electrode array 40 is electrically independent, each conductive wire can be connected in a fashion that allows for impedance measurements using bipolar impedance measurement circuits. For example, the conductive wires can be configured in such a fashion that tetrapolar or guarded tetrapolar electrode configurations can be used. For instance, one pair of conductive wires could function as the current driver and the current return, while another pair of conductive wires could function as a voltage measurement pair.

Accordingly, a dispersive ground pad can function as current return and voltage references. Their placement dictate the current paths and thus having multiple references can also benefit by providing additional paths for determining the ablation status of the tissue. The impedance measurement capability of the device is described in co-pending U.S. Application No.

15/337,334, filed on October 28, 2016 and U.S. Application No. 15/419,269, filed January 30, 2017, the entireties of which are incorporated by reference herein.

FIG. 3B is a side view of the distal tip 16 with the electrode array 40 removed so as to better illustrate a planar surface side 44 of the distal tip 16. As shown in FIG. 3B, the distal- facing edge 46 has a trailing end 50 and a leading end 52, wherein the leading end 52 extends further from the distal tip 16 than the trailing end 50. The cutting wire 42 is positioned along, and generally follows the length of, the distal-facing edge 46. The distal-facing edge 46 may have a length L between 0.5 cm to 5 cm, and, in some embodiments, the length L of the distal- facing edge 46 may be approximately 1 cm. In some embodiments, the distal-facing edge 46 may include a groove 54 formed along a length thereof and configured to receive and provide a guide along which the cutting wire 42 may sit (see FIG. 3D). Accordingly, a portion of the cutting wire 42 adjacent to the leading end 52 of the edge 46 has a relatively small surface area (when compared to the electrode array 40 surface area on side 44), thereby forming an energy focusing portion 48. Thus, because of the arrangement of the cutting wire 42 along the distal- facing edge 46, including the energy-focusing portion 48 at the leading end 52 of the edge 46, the cutting wire can be placed in proximity to the tissue and cut the tissue. In contrast, positioning of the coagulation electrode array 40 on the relatively large surface area of the planar sides or faces 44a, 44b of the distal tip 16 allows the electrode array to coagulate tissue.

It should be noted that the ablation device 14 of the present disclosure may include different distal tip geometries or shapes. For example, FIG. 4 is a perspective view of another embodiment of a distal tip 16b for use with the ablation device 14 of the present invention. As shown, all elements of the ablation device 14 of FIG. 4 are identical to the ablation device 14 illustrated in FIG. 2, while the distal tip 16 has a different shape. FIGS. 5 A and 5B are perspective and side views of the nonconductive distal tip 16b of the ablation device 14 of FIG. 4 in greater detail. In the embodiment shown in FIGS. 5 A and 5B, the distal tip has a more squared-off shape, as opposed to the somewhat rounded off shape of distal tip 16 of FIGS. 2 and 3A-3D. In either case, the distal tip 16b has opposing sides 44 providing a substantially planar surface for the electrode array 40 and a distal-facing edge 46 for the cutting wire 42.

As previously described, the ablation device 14 of the present invention is further configured to provide a conductive fluid, such as saline, to the distal tip 16, which may include one or more ports 45 (e.g., ports through which conductive wires are threaded, additional fluid ports, etc.). The saline weeping through the ports 45 and to an outer surface of the distal tip 16 is able to carry electrical current from electrode array 40 and/or the cutting wire 42, such that energy is transmitted from the electrode array 40, or cutting wire 42, to the tissue by way of the saline weeping from the ports, thereby creating a virtual electrode. Accordingly, upon the fluid weeping through the ports, a pool or thin film of fluid is formed on the exterior surface of the distal tip 16 and is configured to resect and/or coagulate surrounding tissue via the electrical current carried from the electrode array.

As generally understood, the distal tip may be formed from two or more pieces configured to be coupled to one another to form the unitary distal tip 16, such as a configuration, including internal components and connections, as described in co-pending U.S. Application No. 15/337,334, filed on October 28, 2016 and U.S. Application No. 15/419,269, filed January 30, 2017, the entireties of which are incorporated by reference herein, the entireties of which are incorporated by reference.

Reference throughout this specification to "one embodiment" or "an embodiment" means that a particular feature, structure, or characteristic described in connection with the embodiment is included in at least one embodiment. Thus, appearances of the phrases "in one embodiment" or "in an embodiment" in various places throughout this specification are not necessarily all referring to the same embodiment. Furthermore, the particular features, structures, or characteristics may be combined in any suitable manner in one or more embodiments.

The terms and expressions which have been employed herein are used as terms of description and not of limitation, and there is no intention, in the use of such terms and expressions, of excluding any equivalents of the features shown and described (or portions thereof), and it is recognized that various modifications are possible within the scope of the claims. Accordingly, the claims are intended to cover all such equivalents.

As used in any embodiment herein, the term "controller", "module", "subsystem", or the like, may refer to software, firmware and/or circuitry configured to perform any of the aforementioned operations. Software may be embodied as a software package, code, instructions, instruction sets and/or data recorded on non-transitory computer readable storage medium. Firmware may be embodied as code, instructions or instruction sets and/or data that are hard-coded (e.g., nonvolatile) in memory devices. "Circuitry", as used in any embodiment herein, may comprise, for example, singly or in any combination, hardwired circuitry, programmable circuitry such as computer processors comprising one or more individual instruction processing cores, state machine circuitry, and/or firmware that stores instructions executed by programmable circuitry. The controller or subsystem may, collectively or individually, be embodied as circuitry that forms part of a larger system, for example, an integrated circuit (IC), system on-chip (SoC), desktop computers, laptop computers, tablet computers, servers, smart phones, etc.

Any of the operations described herein may be implemented in a system that includes one or more storage mediums having stored thereon, individually or in combination, instructions that when executed by one or more processors perform the methods. Here, the processor may include, for example, a server CPU, a mobile device CPU, and/or other programmable circuitry.

Also, it is intended that operations described herein may be distributed across a plurality of physical devices, such as processing structures at more than one different physical location.

The storage medium may include any type of tangible medium, for example, any type of disk including hard disks, floppy disks, optical disks, compact disk read-only memories (CD-ROMs), compact disk rewritables (CD-RWs), and magneto-optical disks, semiconductor devices such as read-only memories (ROMs), random access memories (RAMs) such as dynamic and static

RAMs, erasable programmable read-only memories (EPROMs), electrically erasable

programmable read-only memories (EEPROMs), flash memories, Solid State Disks (SSDs), magnetic or optical cards, or any type of media suitable for storing electronic instructions.

Other embodiments may be implemented as software modules executed by a programmable control device. The storage medium may be non-transitory.

As described herein, various embodiments may be implemented using hardware elements, software elements, or any combination thereof. Examples of hardware elements may include processors, microprocessors, circuits, circuit elements (e.g., transistors, resistors, capacitors, inductors, and so forth), integrated circuits, application specific integrated circuits

(ASIC), programmable logic devices (PLD), digital signal processors (DSP), field programmable gate array (FPGA), logic gates, registers, semiconductor device, chips, microchips, chip sets, and so forth.

Reference throughout this specification to "one embodiment" or "an embodiment" means that a particular feature, structure, or characteristic described in connection with the embodiment is included in at least one embodiment. Thus, appearances of the phrases "in one embodiment" or "in an embodiment" in various places throughout this specification are not necessarily all referring to the same embodiment. Furthermore, the particular features, structures, or characteristics may be combined in any suitable manner in one or more embodiments. The terms and expressions which have been employed herein are used as terms of description and not of limitation, and there is no intention, in the use of such terms and expressions, of excluding any equivalents of the features shown and described (or portions thereof), and it is recognized that various modifications are possible within the scope of the claims. Accordingly, the claims are intended to cover all such equivalents.