Methods and systems for enhancing ultrasonic visibilty of energy-delivery devices within tissue

Abstract

Electrosurgical systems generally include at least one energy-delivery device for delivering energy to tissue when inserted or embedded within tissue. The energy-delivery device can be a tissue ablation device, such as an ablation probe, needle, etc. for ablating tissue as commonly known in the art. The electrosurgical systems include at least one structure and/or operational characteristic for enhancing ultrasonic visibility of the energy-delivery devices within tissue during ultrasonography.

Claims

1. An electrosurgical system, comprising: a handle assembly; an ablation probe extending distally from the handle assembly, the ablation probe having an outer surface; a vibrating device in mechanical communication with the ablation probe for transmitting vibrational energy to the ablation probe; and at least one wire wrapped around the outer surface for increasing an ultrasonic visibility of the ablation probe.

2. The electrosurgical system according to claim 1, wherein the ablation probe includes a sharpened distal end and the at least one wire is disposed proximally of the sharpened distal end.

3. The electrosurgical system according to claim 1, wherein the at least one wire includes a plurality of wires longitudinally spaced from one another along the ablation probe.

4. The electrosurgical system according to claim 1, wherein the at least one wire is a coil.

5. The electrosurgical system according to claim 1, wherein the ablation probe includes a radiating section and the at least one wire is disposed proximally of the radiating section.

6. The electrosurgical system according to claim 1, wherein the ablation probe includes a radiating section and the at least one wire is disposed on the radiating section.

7. The electrosurgical system according to claim 1, wherein the vibrating device is coupled to the handle assembly.

8. The electrosurgical system according to claim 1, further comprising an eccentric weight connected to the vibrating device.

9. The electrosurgical system according to claim 1, wherein the vibrating device is a motor.

10. The electrosurgical system according to claim 1, further comprising a controller coupled to the handle assembly and configured to adjust a speed of the vibrating device to determine a resonant frequency of the ablation probe.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

(1) Objects and features of the presently-disclosed to methods and systems for enhancing ultrasonic visibility of energy-delivery devices within tissue will become apparent to those of ordinary skill in the art when descriptions of various embodiments thereof are read with reference to the accompanying drawings, of which:

(2) FIG. 1A is a schematic diagram of an electrosurgical system having an energy-delivery device and a vibrating device positioned on a hub in accordance with an embodiment of the present disclosure;

(3) FIG. 1B is a schematic diagram of an electrosurgical system having an energy-delivery device and a vibrating device positioned within a hub in accordance with an embodiment of the present disclosure;

(4) FIG. 2 is a schematic diagram of an electrosurgical system having a handle assembly and a vibrating device positioned within the handle assembly in accordance with an embodiment of the present disclosure;

(5) FIG. 3 is a schematic diagram of an electrosurgical system having a handle assembly and a vibrating device positioned on the handle assembly in accordance with an embodiment of the present disclosure;

(6) FIG. 4 is a schematic diagram of an electrosurgical system having a handle assembly and an energy-delivery device defining an air cavity in accordance with an embodiment of the present disclosure;

(7) FIG. 5 is a schematic diagram of an electrosurgical system having a handle assembly and an energy-delivery device with a metal band in accordance with an embodiment of the present disclosure;

(8) FIG. 6 is a schematic diagram of an electrosurgical system having a handle assembly and an energy-delivery device having a multi-sided distal end in accordance with an embodiment of the present disclosure;

(9) FIG. 7 is a schematic diagram of an electrosurgical system having a handle assembly and an energy-delivery device having a wire wrapped around an outer surface of the energy-delivery device in accordance with an embodiment of the present disclosure;

(10) FIG. 8 is a schematic diagram of an electrosurgical system having a handle assembly and an energy-delivery device having an inflatable balloon in accordance with an embodiment of the present disclosure; and

(11) FIG. 9 is a schematic diagram of an electrosurgical system having a handle assembly and an energy-delivery device having a multi-sided trocar and protrusions at a distal end in accordance with an embodiment of the present disclosure.

DETAILED DESCRIPTION

(12) Hereinafter, embodiments of the presently-disclosed methods and systems for enhancing ultrasonic visibility of energy-delivery devices (or other component) of an electrosurgical system within tissue are described with reference to the accompanying drawings. Like reference numerals may refer to similar or identical elements throughout the description of the figures.

(13) This description may use the phrases “in an embodiment,” “in embodiments,” “in some embodiments,” or “in other embodiments,” which may each refer to one or more of the same or different embodiments in accordance with the present disclosure. For the purposes of this description, a phrase in the form “A/B” means A or B. For the purposes of the description, a phrase in the form “A and/or B” means “(A), (B), or (A and B)”. For the purposes of this description, a phrase in the form “at least one of A, B, or C” means “(A), (B), (C), (A and B), (A and C), (B and C), or (A, B and C)”.

(14) In accordance with the present disclosure, electrosurgical systems are provided generally including at least one energy-delivery device for delivering energy to tissue when inserted or embedded within tissue. The electrosurgical systems include at least one structure and/or operational characteristic for enhancing ultrasonic visibility of the energy-delivery devices within tissue during ultrasonography.

(15) Enhancing the ultrasonic visibility of the energy-delivery device using an ultrasonic imaging system is beneficial for aiding in the placement of the energy-delivery devices during percutaneous and surgical procedures. This is because there is very little ultrasonic contrast between the tissue and energy-delivery devices which makes it difficult to distinguish energy-delivery devices as they pass through the tissue.

(16) The energy-delivery device can be a tissue ablation device, such as an ablation probe, needle, etc. for ablating tissue as commonly known in the art. The ablation probe, for exemplary purposes in describing the various embodiments of the present disclosure, is an ablation probe including a fluid-cooled antenna assembly.

(17) Additionally, the electrosurgical system described herein for exemplary purposes includes a thermal-feedback that controls the rate of fluid flow to the ablation probe. It is contemplated that embodiments of the present disclosure for enhancing ultrasonic visibility of energy-delivery devices or other components of the electrosurgical system within tissue can be implemented, integrated and/or otherwise incorporated in other systems and energy-delivery devices which are not described or mentioned herein. The description of the embodiments of the present disclosure to certain systems, especially electrosurgical systems, is for exemplary purposes only and shall not be construed as limiting the embodiments described herein to only these systems and variants thereof. That is, for example, embodiments may be implemented using electromagnetic radiation at microwave frequencies or at other frequencies.

(18) According to various embodiments, the electrosurgical system is designed and configured to operate between about 300 MHz and about 10 GHz. Systems for enhancing ultrasonic visibility of an energy-delivery device, as described herein, may be used in conjunction with various types of devices, such as microwave antenna assemblies having either a straight or looped radiating antenna portion, etc., which may be inserted into tissue to be treated.

(19) Various embodiments of the presently-disclosed electrosurgical systems utilizing methods and systems for enhancing ultrasonic visibility of an energy-delivery device are suitable for microwave ablation and for use to pre-coagulate tissue for microwave ablation-assisted surgical resection. Although various methods and systems described herein below are targeted toward ablation and the complete destruction of target tissue, it is to be understood that methods for directing electromagnetic radiation may be used with other therapies in which the target tissue is partially destroyed or damaged, such as, for example, to prevent the conduction of electrical impulses within heart tissue.

(20) FIG. 1A shows an electrosurgical system 10 according to an embodiment of the present disclosure that includes an energy-delivery device in the form of an ablation probe 100, an electrosurgical power generating source 28, e.g., a microwave or RF electrosurgical generator, and an electrolysis assembly 84 in fluid communication with a distal end of the energy-delivery device 100. The electrolysis assembly 84 enables the generation and release of bubbles at a distal end of the ablation probe 100 for enhancing ultrasonic visibility according to one embodiment of the present disclosure.

(21) The bubbles are produced by the electrolysis assembly 84 through electrolysis using an anode and cathode arrangement. The bubbles enhance the ultrasonic visibility of the ablation probe 100 during ultrasonography. The bubbles reflect ultrasonic energy delivered by an ultrasonic generator during ultrasonography making them brighter in contrast compared to surrounding tissue and the ablation probe. Accordingly, by noticing the brighter contrast, one can determine the location and position of the distal end of the ablation probe 100 within tissue.

(22) The electrosurgical system 10 further includes a feedback control system 14 operably associated with a coolant supply system 11. Probe 100 is operably coupled to the electrosurgical power generating source 28, and disposed in fluid communication with the coolant supply system 11.

(23) In some embodiments, one or more components of the coolant supply system 11 may be integrated fully or partially into the electrosurgical power generating source 28. Coolant supply system 11, which is described in more detail later in this description, is adapted to provide coolant fluid “F” to the probe 100. Probe 100, which is described in more detail later in this description, may be integrally associated with a hub 142 configured to provide electrical and/or coolant connections to the probe 100.

(24) In some embodiments, the electrosurgical system 10 includes one or more sensors capable of generating a signal indicative of a temperature of a medium in contact therewith (referred to herein as temperature sensors) and/or one or more sensors capable of generating a signal indicative of a rate of fluid flow (referred to herein as flow sensors). In such embodiments, the feedback control system 14 may be adapted to provide a thermal-feedback-controlled rate of fluid flow to the probe 100 using one or more signals output from one or more temperature sensors and/or one or more flow sensors operably associated with the probe 100 and/or conduit fluidly-coupled to the probe 100.

(25) The probe 100 as shown by FIG. 1A includes a strain relief 200. The strain relief 200 is fixed to a surface of the hub 142 to counter mechanical stress when the probe 100 bends during an electrosurgical procedure. In some embodiments, the probe 100 may extend from a handle assembly as shown by several of the figures.

(26) In embodiments according to the present disclosure, as shown by FIGS. 1A and 1B, ultrasonic visibility of the energy-delivery device, such as the ablation probe 100, within tissue is enhanced by mechanical vibration. The electrosurgical system 10 of FIG. 1A is provided with a motor 202. The motor 202 is positioned on hub 142 from which the ablation probe 100 extends from. The motor 202 can include an eccentric weight 204. The motor 202 and eccentric weight 204 cause mechanical vibration energy to be transferred or transmitted from the proximal end of the ablation probe 100 to the distal end of the ablation probe 100 when the motor 202 is actuated. The mechanical vibration energy causes ablation probe 100, including its distal end, to vibrate. A vibrating distal end of the ablation probe 100 has greater ultrasonic visibility than a non-vibrating distal end.

(27) The motor 202 can also be positioned inside the hub 142 as shown by FIG. 1B. When the motor 202 is positioned within the hub 142, an eccentric weight 204A can be provided at a distal end of the ablation probe 100. The eccentric weight 204A is mechanically connected to the motor 202 via a mechanical linkage assembly 206, such as a rigid rod, designed to transfer mechanical vibration energy from the motor 202 to the eccentric weight 204A. The mechanical vibration energy causes the eccentric weight 204A at the distal end of the probe 100 to vibrate, and thereby impart vibrational energy to the distal end of the ablation probe 100. The vibrational energy causes the ablation probe 100, especially its distal end, to vibrate, and thereby increase the ultrasonic visibility of the probe 100.

(28) FIGS. 2-4 illustrate an electrosurgical system 10A having a handle assembly 208. In a first embodiment shown by FIG. 2, the handle assembly 208 is provided therein with a motor 210, similar to the embodiment shown by FIG. 1B. The motor 210 can be a high speed motor as known in the art. The motor 210 is in operative communication with an eccentric weight 212 positioned at a distal end of an ablation probe 214.

(29) The eccentric weight 212 is mechanically connected to the motor 210 via a mechanical linkage assembly 216 designed to transfer mechanical vibration energy from the motor 210 through a longitudinal member 213, such as a shaft or cooling jacket, of the probe 214 to the eccentric weight 212. The linkage assembly 216 can include one or more rigid rods. The mechanical vibration energy causes the eccentric weight 212 to vibrate, and thereby impart vibrational energy to a distal end 211 of the ablation probe 214. The vibrational energy causes the ablation probe 214, especially its distal end 211, to vibrate, and thereby increase the ultrasonic visibility of the probe 214. The handle assembly 208 can include one or more controls 217 for operating the ablation probe 214 of the electrosurgical system, including actuating the motor 210 or other vibrating device during ultrasonography.

(30) The motor 210 can also be on the handle assembly 208 as shown by FIG. 3, similar to positioning the motor 210 on the hub 142 as shown by FIG. 1A. When the motor 210 is positioned on the handle assembly 208, an eccentric weight 212A can be connected thereto via a mechanical connection 219, such as at least one rigid rod. Activation of the motor 210 transfers mechanical vibration energy via a longitudinal member 213, such as a shaft or cooling jacket, of the probe 214 to the distal end 211 of the probe 214. The mechanical vibration energy causes the distal end 211 of the ablation probe 214 to vibrate, and thereby increase the ultrasonic visibility of the probe 214. A vibrating distal end of the ablation probe 214 has greater ultrasonic visibility than a non-vibrating distal end.

(31) Variations of the above described mechanical vibration embodiments include using the controls 217 or a controller, such as a processor, to perform at least one of the following: adjusting the speed of the motor or other vibrating device to determine the resonant frequency of the energy-delivery devices 100, 214, and adjusting the speed of the motor 210 to determine the harmonic frequency of the ultrasonic imaging system in operative communication with the electrosurgical system.

(32) It is contemplated that the electrosurgical systems can include a controller, such as a processor, for performing at least two or more of the mechanical vibrating actions described above for vibrating the energy-delivery device, such as, for example, rapidly varying or sweeping the frequency to allow the energy-delivery device to continually pass through the resonant frequency of the energy-delivery device or harmonic frequency of the ultrasonic imaging system used for performing ultrasonography.

(33) In embodiments, vibration of the energy-delivery device can be achieved by the use of other vibrating devices, besides a motor, capable of generating mechanical vibrational energy, such as micro-machines, IC chip, electromagnet, etc.

(34) In the embodiments of the electrosurgical system 10 shown in FIGS. 1A and 1B, a processor unit 82 is disposed within or otherwise associated with the electrosurgical power generating source 28. Processor unit 82 may be communicatively-coupled to one or more components or modules of the electrosurgical power generating source 28, e.g., a user interface 121 and a generator module 86. Processor unit 82 may additionally, or alternatively, be communicatively-coupled to one or more temperature sensors (e.g., two sensors “TS.sub.1” and “TS.sub.2” shown in FIGS. 1A and 1B) and/or one or more flow sensors (e.g., one sensor “FS.sub.1” shown in FIGS. 1A and 1B) for receiving one or more signals indicative of a temperature (referred to herein as temperature data) and/or one or more signals indicative of a flow rate (referred to herein as flow data). Transmission lines may be provided to electrically couple the temperature sensors, flow sensors and/or other sensors, e.g., pressure sensors, to the processor unit 82.

(35) Electrosurgical power generating source 28 may include any generator suitable for use with electrosurgical devices, and may be configured to provide various frequencies of electromagnetic energy. In some embodiments, the electrosurgical power generating source 28 is configured to provide microwave energy at an operational frequency from about 300 MHz to about 10 GHz. In some embodiments, the electrosurgical power generating source 28 is configured to provide electrosurgical energy at an operational frequency from about 400 KHz to about 500 KHz.

(36) Probe 100 may include one or more antennas of any suitable type, such as an antenna assembly (or antenna array) suitable for use in tissue ablation applications. For ease of explanation and understanding, the probe 100 is described as including a single antenna assembly 112. In some embodiments, the antenna assembly 112 is substantially disposed within a sheath 138. Probe 100 generally includes a coolant chamber 137 defined about the antenna assembly 112. In some embodiments, the coolant chamber 137 includes an interior lumen defined by the sheath 138.

(37) Probe 100 may include a feedline 110 coupled to the antenna assembly 112. A transmission line 16 may be provided to electrically couple the feedline 110 to the electrosurgical power generating source 28. Feedline 110 may be coupled to a connection hub 142, which is described in more detail later in this description, to facilitate the flow of coolant and/or buffering fluid into, and out of, the probe 100.

(38) In the embodiments shown in FIGS. 1A and 1B and in accordance with the present disclosure, the feedback control system 14 is operably associated with a flow-control device 50 disposed in fluid communication with a fluid flow path of the coolant supply system 11 (e.g., first coolant path 19) fluidly-coupled to the probe 100. Flow-control device 50 may include any suitable device capable of regulating or controlling the rate of fluid flow passing though the flow-control device 50, or selectively blocking the fluid flow, e.g., a valve of any suitable type operable to selectively impede or restrict flow of fluid through passages in the valve, for among other purposes, causing hydraulic energy in the form of high pressure pulses to be transferred or transmitted to the ablation probe 100.

(39) The hydraulic energy is transferred or transmitted via the fluid flow path thorough the ablation probe 100 causing the ablation probe 100 to vibrate. The vibration of the ablation probe 100 enhances its ultrasonic visibility. It is envisioned that one or more additional flow-control devices can be positioned at different locations along the fluid flow path, including on the ablation probe 100, for selectively blocking and unblocking the fluid flow for transferring hydraulic energy to the ablation probe 100, especially to tapered portion 120 of the ablation probe 100. The hydraulic energy causes vibration of the ablation probe 100 which enhances its ultrasonic visibility.

(40) In embodiments, the flow-control device 50 may include a valve 52 having a valve body 54 and an electromechanical actuator 56 operatively-coupled to the valve body 54. Valve body 54 may be implemented as a ball valve, gate valve, butterfly valve, plug valve, or any other suitable type of valve. In the embodiments shown in FIGS. 1A and 1B, the actuator 56 is communicatively-coupled to with the processor unit 82 via a transmission line 32. Processor unit 82 may be configured to control the flow-control device 50 by activating the actuator 56 to selectively block fluid flow, or adjust the fluid flow rate in a fluid flow path (e.g., first coolant path 19 of the coolant supply system 11) fluidly-coupled to the connection hub 142 to achieve a desired fluid flow rate. The amount of time the fluid flow is blocked or the desired fluid flow rate may be determined by a computer program and/or logic circuitry associated with the processor unit 82. The amount of time the fluid flow is blocked or the desired fluid flow rate may additionally, or alternatively, be selected from a look-up table or determined by a computer algorithm.

(41) In other embodiments according to the present disclosure, controls can be used to control the speed of a pump for creating high pressure pulses to be transferred or transmitted to the ablation probe 100. For example, a multi-speed pump can be provided on the fluid flow path, similar to fluid-movement device 60 described further below, instead of a valve, and the processor unit 82 may be configured to vary the pump speed to selectively adjust the fluid flow rate to attain a desired fluid flow rate, and to selectively turn on and off the pump.

(42) At higher pumping speeds, the fluid pressure of the circulating cooling fluid through the energy-delivery device is increased, thereby causing increased vibration of the energy-delivery device 100. The speed of the pump can also be adjusted to determine the resonant frequency of the energy-delivery device 100 or the harmonic frequency of the ultrasonic imaging system performing the ultrasonography.

(43) In another embodiment of the present disclosure, the electrosurgical system 10 includes a pulsating device in operative communication with the pump. The pulsating device rapidly alternates the direction of fluid flow for achieving maximum hydraulic pressure change within the energy-delivery device 100 and vibration of the energy-delivery device 100. The vibration of the energy-delivery device 100 enhances the ultrasonic visibility of the energy-delivery device 100.

(44) In still another embodiment of the present disclosure, the electrosurgical system 10 performs at least two or more of the hydraulic vibrating actions described above for vibrating the energy-delivery device 100, such as, for example, blocking the fluid flow while a controller, such as a processor, rapidly varies or sweeps the frequency to allow the energy-delivery device 100 to continually pass through the resonant frequency (or harmonic frequency) of the ultrasonic imaging system.

(45) Processor unit 82 may also be configured to control the flow-control device 50 based on determination of a desired fluid flow rate using temperature data received from one or more temperature sensors (e.g., “TS.sub.1” and “TS.sub.2”).

(46) With continued reference to FIGS. 1A and 1B, electrosurgical system 10 includes a suitable pressure-relief device 40 disposed in fluid communication with the diversion flow path 21 which may allow the fluid-movement device 60 to run at a substantially constant speed and/or under a near-constant load (head pressure) regardless of the selective adjustment of the fluid flow rate in the first coolant path 19. Utilizing the suitable pressure-relief device 40 disposed in fluid communication with the diversion flow path 21, in accordance with the present disclosure, may allow the fluid-movement device 60 to be implemented as a single speed device, e.g., a single speed pump.

(47) Feedback control system 14 may utilize data “D” (e.g., data representative of a mapping of temperature data to settings for properly adjusting one or more operational parameters of the flow-control device 50 to achieve a desired temperature and/or a desired ablation) stored in a look-up table, or other data structure, to determine the desired fluid flow rate. In the embodiments shown in FIGS. 1A and 1B, the electrosurgical system 10 includes a first temperature sensor “TS.sub.1” capable of generating a signal indicative of a temperature of a medium in contact therewith and a second temperature sensor “TS.sub.2” capable of generating a signal indicative of a temperature of a medium in contact therewith. Feedback control system 14 may be configured to utilize signals received from the first temperature sensor “TS.sub.1” and/or the second temperature sensor “TS.sub.2” to control the flow-control device 50.

(48) In some embodiments, the electrosurgical system 10 includes a flow sensor “FS.sub.1” communicatively-coupled to the processor unit 82, e.g., via a transmission line 36. In some embodiments, the flow sensor “FS.sub.1” may be disposed in fluid communication with the first coolant path 19 or the second coolant path 20. Processor unit 82 may be configured to control the flow-control device 50 based on determination of a desired fluid flow rate using one or more signals received from the flow sensor “FS.sub.1”. In some embodiments, the processor unit 82 may be configured to control the flow-control device 50 based on determination of a desired fluid flow rate using one or more signals received from the flow sensor “FS.sub.1” in conjunction with one or more signals received from the first temperature sensor “TS.sub.1” and/or the second temperature sensor “TS.sub.2”. Although the electrosurgical system 10 shown in FIGS. 1A and 1B includes one flow sensor “FS.sub.1”, alternative embodiments may be implemented with a plurality of flow sensors adapted to provide a measurement of the rate of fluid flow into and/or out of the probe 100 and/or conduit fluidly-coupled to the probe 100.

(49) Electrosurgical system 10 may additionally, or alternatively, include one or more pressure sensors adapted to provide a measurement of the fluid pressure in the probe 100 and/or conduit fluidly-coupled the probe 100. In some embodiments, the electrosurgical system 10 includes one or more pressure sensors (e.g., pressure sensor 70) disposed in fluid communication with one or more fluid flow paths (e.g., first coolant path 19) of the coolant supply system 11 as opposed to a pressure sensor disposed within the probe 100, reducing cost and complexity of the probe 100.

(50) In the embodiments shown in FIGS. 1A and 1B, the processor unit 82 is operably associated with a pressure sensor 70 disposed in fluid communication with a fluid flow path of the coolant supply system 11. Processor unit 82 may be communicatively-coupled to the pressure sensor 70 via a transmission line 30 or wireless link. Processor unit 82 may additionally, or alternatively, be operably associated with one or more pressure sensors disposed within the probe 100, e.g., disposed in fluid communication with the coolant chamber 137, for monitoring the fluid flow pressure within the probe 100.

(51) Pressure sensor 70 may include any suitable type of pressure sensor, pressure transducer, pressure transmitter, or pressure switch. Pressure sensor 70 (also referred to herein as “pressure transducer”) may include a variety of components, e.g., resistive elements, capacitive elements and/or piezo-resistive elements, and may be disposed at any suitable position in the coolant supply system 11. In some embodiments, the pressure transducer 70 is disposed in fluid communication with the first coolant path 19 located between the fluid-movement device 60 and the flow-control device 50, e.g., placed at or near the flow-control device 50.

(52) In some embodiments, the processor unit 82 may be configured to control the flow-control device 50, and/or other valve controlling fluid flow for transferring hydraulic energy to the ablation probe 100, based on determination of a desired fluid flow rate using pressure data received from one or more pressure sensors and/or vibration data received from one or more accelerometers 232. The one or more accelerometers can be positioned at a distal end of the probe 100 as shown by FIGS. 1A and 1B.

(53) In some embodiments, the processor unit 82 may be configured to control the flow-control device 50 based on determination of a desired fluid flow rate using one or more signals received from the first temperature sensor “TS.sub.1” and/or the second temperature sensor “TS.sub.2” and/or the flow sensor “FS.sub.1” in conjunction with one or more signals received from the pressure transducer 70 and/or one or more accelerometers 232. The one or more accelerometers may be positioned on the probe 100 for monitoring the amount of vibration or displacement of the probe 100 from its axis, such as its longitudinal axis.

(54) In some embodiments, the processor unit 82 may be configured to control the amount of power delivered to the antenna assembly 112 based on time and power settings provided by the user in conjunction with sensed temperature signals indicative of a temperature of a medium, e.g., coolant fluid “F”, in contact with one or one temperature sensors operably associated with the antenna assembly 112 and/or the connection hub 142. In some embodiments, the processor unit 82 may be configured to decrease the amount of power delivered to the antenna assembly 112 when sensed temperature signals indicative of a temperature below a predetermined temperature threshold are received by processor unit 82, e.g., over a predetermined time interval.

(55) Processor unit 82 may be configured to control one or more operating parameters associated with the electrosurgical power generating source 28 based on determination of whether the pressure level of fluid in the probe 100 and/or conduit fluidly-coupled to the probe 100 is above a predetermined threshold using pressure data received from one or more pressure sensors, e.g., pressure transducer 70. Examples of operating parameters associated with the electrosurgical power generating source 28 include without limitation temperature, impedance, power, current, voltage, mode of operation, and duration of application of electromagnetic energy.

(56) In some embodiments, the output signal of the pressure transducer 70, representing a pressure value and possibly amplified and/or conditioned by means of suitable components (not shown), is received by the processor unit 82 and used for determination of whether the pressure level of fluid in the probe 100 and/or conduit fluidly-coupled to the probe 100 is above a predetermined threshold in order to control when power is delivered to the antenna assembly 112. In some embodiments, in response to a determination that the pressure level of fluid in the probe 100 and/or conduit fluidly-coupled to the probe 100 is below the predetermined threshold, the processor unit 82 may be configured to decrease the amount of power delivered to the antenna assembly 112 and/or to stop energy delivery between the electrosurgical power generating source 28 and the probe 100. In some embodiments, the processor unit 82 may be configured to enable energy delivery between the electrosurgical power generating source 28 and the probe 100 based on determination that the pressure level of fluid in the probe 100 and/or conduit fluidly-coupled to the probe 100 is above the predetermined threshold.

(57) In some embodiments, the pressure transducer 70 is adapted to output a predetermined signal to indicate a sensed pressure below that of the burst pressure of the pressure-relief device 40. A computer program and/or logic circuitry associated with the processor unit 82 may be configured to enable the electrosurgical power generating source 28 and the flow-control device 50 in response to a signal from the pressure transducer 70. A computer program and/or logic circuitry associated with the processor unit 82 may be configured to output a signal indicative of an error code and/or to activate an indicator unit 129 if a certain amount of time elapses between the point at which energy delivery to the probe 100 is enabled and when the pressure signal is detected, e.g., to ensure that the fluid-movement device 60 is turned on and/or that the probe 100 is receiving flow of fluid before the antenna assembly 112 can be activated.

(58) As shown in FIGS. 1A and 1B, a feedline 110 couples the antenna assembly 112 to a connection hub 142. Connection hub 142 may have a variety of suitable shapes, e.g., cylindrical, rectangular, etc. Connection hub 142 generally includes a hub body 145 defining an outlet fluid port 177 and an inlet fluid port 179. Hub body 145 may include one or more branches, e.g., three branches 164, 178 and 176, extending from one or more portions of the hub body 145. In some embodiments, one or more branches extending from the hub body 145 may be configured to house one or more connectors and/or ports, e.g., to facilitate the flow of coolant and/or buffering fluid into, and out of, the connection hub 142.

(59) In the embodiments shown in FIGS. 1A and 1B, the hub body 145 includes a first branch 164 adapted to house a cable connector 165, a second branch 178 adapted to house the inlet fluid port 179, and a third branch 176 adapted to house the outlet fluid port 177. It is to be understood, however, that other connection hub embodiments may also be used. Examples of hub embodiments are disclosed in commonly assigned U.S. Pat. No. 8,118,808, entitled “COOLED DIELECTRICALLY BUFFERED MICROWAVE DIPOLE ANTENNA”, and U.S. Pat. No. 7,311,703, entitled “DEVICES AND METHODS FOR COOLING MICROWAVE ANTENNAS”; the contents of both are incorporated herein by reference.

(60) In some embodiments, the flow sensor “FS.sub.1” is disposed in fluid communication with the first coolant path 19, e.g., disposed within the inlet fluid port 179 or otherwise associated with the second branch 178, and the second temperature sensor “TS.sub.2” is disposed in fluid communication with the second coolant path 20, e.g., disposed within the outlet fluid port 177 or otherwise associated with the third branch 176. In other embodiments, the second temperature sensor “TS.sub.2” may be disposed within the inlet fluid port 179 or otherwise associated with the second branch 178, and the flow sensor “FS.sub.1” may be disposed within the outlet fluid port 177 or otherwise associated with the third branch 176.

(61) Coolant supply system 11 generally includes a substantially closed loop having a first coolant path 19 leading to the probe 100 and a second coolant path 20 leading from the probe 100, a coolant source 90, and the fluid-movement device 60, e.g., disposed in fluid communication with the first coolant path 19. In some embodiments, the coolant supply system 11 includes a third coolant path 21 (also referred to herein as a “diversion flow path”) disposed in fluid communication with the first coolant path 19 and the second coolant path 20. The conduit layouts of the first coolant path 19, second coolant path 20 and third coolant path 21 may be varied from the configuration depicted in FIGS. 1A and 1B.

(62) In some embodiments, a pressure-relief device 40 may be disposed in fluid communication with the diversion flow path 21. Pressure-relief device 40 may include any type of device, e.g., a spring-loaded pressure-relief valve, adapted to open at a predetermined set pressure and to flow a rated capacity at a specified over-pressure. In some embodiments, one or more flow-restrictor devices (not shown) suitable for preventing backflow of fluid into the first coolant path 19 may be disposed in fluid communication with the diversion flow path 21. Flow-restrictor devices may include a check valve or any other suitable type of unidirectional flow restrictor or backflow preventer, and may be disposed at any suitable position in the diversion flow path 21 to prevent backflow of fluid from the diversion flow path 21 into the first coolant path 19.

(63) In some embodiments, the first coolant path 19 includes a first coolant supply line 66 leading from the coolant source 90 to the fluid-movement device 60, a second coolant supply line 67 leading from the fluid-movement device 60 to the flow-control device 50, and a third coolant supply line 68 leading from the flow-control device 50 to the inlet fluid port 179 defined in the second branch 178 of the connection hub body 145, and the second coolant path 20 includes a first coolant return line 95 leading from the outlet fluid port 177 defined in the third branch 176 of the hub body 145 to the coolant source 90. Embodiments including the diversion flow path 21 may include a second coolant return line 94 fluidly-coupled to the second coolant supply line 67 and the first coolant return line 95. Pressure-relief device 40 may be disposed at any suitable position in the second coolant return line 94. The spacing and relative dimensions of coolant supply lines and coolant return lines may be varied from the configuration depicted in FIGS. 1A and 1B.

(64) Coolant source 90 may be any suitable housing containing a reservoir of coolant fluid “F”. Coolant fluid “F” may be any suitable fluid that can be used for cooling or buffering the probe 100, e.g., deionized water, or other suitable cooling medium. Coolant fluid “F” may have dielectric properties and may provide dielectric impedance buffering for the antenna assembly 112. Coolant fluid “F” may be a conductive fluid, such as a saline solution, which may be delivered to the target tissue, e.g., to decrease impedance and allow increased power to be delivered to the target tissue. A coolant fluid “F” composition may vary depending upon desired cooling rates and the desired tissue impedance matching properties. Various fluids may be used, e.g., liquids including, but not limited to, water, saline, perfluorocarbon, such as the commercially available Fluorinert® perfluorocarbon liquid offered by Minnesota Mining and Manufacturing Company (3M), liquid chlorodifluoromethane, etc. In other variations, gases (such as nitrous oxide, nitrogen, carbon dioxide, etc.) may also be utilized as the cooling fluid. In yet another variation, a combination of liquids and/or gases, including, for example, those mentioned above, may be utilized as the coolant fluid “F”.

(65) In the embodiments shown in FIGS. 1A and 1B, the fluid-movement device 60 is provided in the first coolant path 19 to move the coolant fluid “F” through the first coolant path 19 and into, and out of, the probe 100. Fluid-movement device 60 may include valves, pumps, power units, actuators, fittings, manifolds, etc. The position of the fluid-movement device 60, e.g., in relation to the coolant source 90, may be varied from the configuration depicted in FIGS. 1A and 1B. Although the coolant supply system 11 shown in FIGS. 1A and 1B includes a single, fluid-movement device 60 located in the first coolant path 19, various combinations of different numbers of fluid-movement devices, variedly-sized and variedly-spaced apart from each other, may be provided in the first coolant path 19 and/or the second coolant path 20.

(66) In some embodiments, the probe 100 includes a feedline 110 that couples the antenna assembly 112 to a hub, e.g., connection hub 142, that provides electrical and/or coolant connections to the probe 100. Feedline 110 may be formed from a suitable flexible, semi-rigid or rigid microwave conductive cable. Feedline 110 may be constructed of a variety of electrically-conductive materials, e.g., copper, gold, or other conductive metals with similar conductivity values. Feedline 110 may be made of stainless steel, which generally offers the strength required to puncture tissue and/or skin.

(67) In some variations, the antenna assembly 112 includes a distal radiating portion 105 and a proximal radiating portion 140. In some embodiments, a junction member (not shown), which is generally made of a dielectric material, couples the proximal radiating section 140 and the distal radiating section 105. In some embodiments, the distal and proximal radiating sections 105, 140 align at the junction member and are also supported by an inner conductor (not shown) that extends at least partially through the distal radiating section 105.

(68) Antenna assembly 112 or probe 214 may be provided with an end cap or tapered portion 120, which may terminate in a sharp tip 123 to allow for insertion into tissue with minimal resistance. One example of a straight probe with a sharp tip that may be suitable for use is commercially available under the trademark EVIDENT™ offered by Covidien. The end cap or tapered portion 120 may include other shapes, such as, for example, a tip 123 that is rounded, flat, square, hexagonal, or cylindroconical. End cap or tapered portion 120 may be formed of a material having a high dielectric constant, and may be a trocar.

(69) Sheath 138 generally includes an outer jacket 139 defining a lumen into which the antenna assembly 112, or portion thereof, may be positioned. In some embodiments, the sheath 138 is disposed over and encloses the feedline 110, the proximal radiating portion 140 and the distal radiating portion 105, and may at least partially enclose the end cap or tapered portion 120. The outer jacket 139 may be formed of any suitable material, such as, for example, polymeric or ceramic materials. The outer jacket 139 may be a water-cooled catheter formed of a material having low electrical conductivity.

(70) In accordance with the embodiments shown in FIGS. 1A and 1B, a coolant chamber 137 is defined by the outer jacket 139 and the end cap or tapered portion 120. Coolant chamber 137 is disposed in fluid communication with the inlet fluid port 179 and the outlet fluid port 177 and adapted to circulate coolant fluid “F” therethrough, and may include baffles, multiple lumens, flow restricting devices, or other structures that may redirect, concentrate, or disperse flow depending on their shape. Examples of coolant chamber embodiments are disclosed in commonly assigned U.S. Pat. No. 8,945,111, entitled “CHOKED DIELECTRIC LOADED TIP DIPOLE MICROWAVE ANTENNA”, commonly assigned U.S. Pat. No. 8,118,808, entitled “COOLED DIELECTRICALLY BUFFERED MICROWAVE DIPOLE ANTENNA”, and U.S. Pat. No. 7,311,703, entitled “DEVICES AND METHODS FOR COOLING MICROWAVE ANTENNAS”, the contents of these references are incorporated herein by reference. The size and shape of the sheath 138 and the coolant chamber 137 extending therethrough may be varied from the configuration depicted in FIGS. 1A and 1B.

(71) During microwave ablation, e.g., using the electrosurgical system 10, the probe 100 is inserted into or placed adjacent to tissue and microwave energy is supplied thereto. Ultrasonography is used to accurately guide the probe 100 into the area of tissue to be treated in accordance with the present disclosure. Probe 100 may be placed percutaneously or atop tissue, e.g., using conventional surgical techniques by surgical staff. A clinician may pre-determine the length of time that microwave energy is to be applied. Application duration may depend on many factors such as tumor size and location and whether the tumor was a secondary or primary cancer. The duration of microwave energy application using the probe 100 may depend on the progress of the heat distribution within the tissue area that is to be destroyed and/or the surrounding tissue. Single or multiple probes 100 may be used to provide ablations in short procedure times, e.g., a few seconds to minutes, to destroy cancerous cells in the target tissue region.

(72) A plurality of probes 100 may be placed in variously arranged configurations to substantially simultaneously ablate a target tissue region, making faster procedures possible. Multiple probes 100 can be used to synergistically create a large ablation or to ablate separate sites simultaneously. Tissue ablation size and geometry is influenced by a variety of factors, such as the energy applicator design, number of energy applicators used simultaneously, time and wattage.

(73) In operation, microwave energy having a wavelength, lambda (λ), is transmitted through the antenna assembly 112, e.g., along the proximal and distal radiating portions 140, 105, and radiated into the surrounding medium, e.g., tissue. The length of the antenna for efficient radiation may be dependent on the effective wavelength λ.sub.eff which is dependent upon the dielectric properties of the medium being radiated. Antenna assembly 112, through which microwave energy is transmitted at a wavelength λ, may have differing effective wavelengths λ.sub.eff depending upon the surrounding medium, e.g., liver tissue as opposed to breast tissue.

(74) In some embodiments, the electrosurgical system 10 includes a first temperature sensor “TS.sub.1” disposed within a distal radiating portion 105 of the antenna assembly 112. First temperature sensor “TS.sub.1” may be disposed within or contacting the end cap or tapered portion 120. It is to be understood that the first temperature sensor “TS.sub.1” may be disposed at any suitable position to allow for the sensing of temperature. Processor unit 82 may be electrically connected by a transmission line 34 to the first temperature sensor “TS.sub.1”. Sensed temperature signals indicative of a temperature of a medium in contact with the first temperature sensor “TS.sub.1” may be utilized by the processor unit 82 to control the flow of electrosurgical energy and/or the flow rate of coolant to attain the desired ablation.

(75) Electrosurgical system 10 may additionally, or alternatively, include a second temperature sensor “TS.sub.2” disposed within the outlet fluid port 177 or otherwise associated with the third branch 176 of the hub body 145. Processor unit 82 may be electrically connected by a transmission line 38 to the second temperature sensor “TS.sub.2”. First temperature sensor “TS.sub.1” and/or the second temperature sensor “TS.sub.2” may be a thermocouple, thermistor, or other temperature sensing device. A plurality of sensors may be utilized including units extending outside the tip 123 to measure temperatures at various locations in the proximity of the tip 123.

(76) As described in US Patent Publication No. US2012-0232549, which is commonly-owned, a memory device in operable connection with the processor unit 82 can be provided. In some embodiments, the memory device may be associated with the electrosurgical power generating source 28. The memory device may also be implemented as a storage device integrated into the electrosurgical power generating source 28. In some embodiments, the memory device may be implemented as an external device communicatively-coupled to the electrosurgical power generating source 28.

(77) The processor unit 82 may be communicatively-coupled to the flow-control device 50, e.g., via a transmission line, and may be communicatively-coupled to the fluid-movement device 60, e.g., via a transmission line. In some embodiments, the processor unit 82 may be configured to control one or more operational parameters of the fluid-movement device 60 to selectively adjust the fluid flow rate in a fluid flow path (e.g., first coolant path 19) of the coolant supply system 11. In one non-limiting example, the fluid-movement device 60 is implemented as a multi-speed pump, and the processor unit 82 may be configured to vary the pump speed to selectively adjust the fluid flow rate to attain a desired fluid flow rate.

(78) Processor unit 82 may be configured to execute a series of instructions to control one or more operational parameters of the flow-control device 50 based on determination of a desired fluid flow rate using temperature data received from one or more temperature sensors, e.g., “TS.sub.1” and “TS.sub.2”. The temperature data may be transmitted via transmission lines or wirelessly transmitted. One or more flow sensors may additionally, or alternatively, be communicatively-coupled to the processor unit 82, e.g., via transmission lines. In some embodiments, signals indicative of the rate of fluid flow into and/or out of the probe 100 and/or conduit fluidly-coupled the probe 100 received from one or more flow sensors may be used by the processor unit 82 to determine a desired fluid flow rate. In such embodiments, flow data may be used by the processor unit 82 in conjunction with temperature data, or independently of temperature data, to determine a desired fluid flow rate. The desired fluid flow rate may be selected from a look-up table or determined by a computer algorithm stored within the memory device.

(79) In some embodiments, an analog signal that is proportional to the temperature detected by a temperature sensor, e.g., a thermocouple, may be taken as a voltage input that can be compared to a look-up table for temperature and fluid flow rate, and a computer program and/or logic circuitry associated with the processor unit 82 may be used to determine the needed duty cycle of the pulse width modulation (PWM) to control actuation of a valve (e.g., valve 52) to attain the desired fluid flow rate. Processor unit 82 may be configured to execute a series of instructions such that the flow-control device 50 and the fluid-movement device 60 are cooperatively controlled by the processor unit 82, e.g., based on determination of a desired fluid flow rate using temperature data and/or flow data, to selectively adjust the fluid flow rate in a fluid flow path (e.g., first coolant path 19) of the coolant supply system 11.

(80) Feedback control system 14 may be adapted to control the flow-control device 50 to allow flow (e.g., valve 52 held open) for longer periods of time as the sensed temperature rises, and shorter periods of time as the sensed temperature falls. Electrosurgical system 10 may be adapted to override PWM control of the flow-control device 50 to hold the valve 52 open upon initial activation of the antenna assembly 112. For this purpose, a timer may be utilized to prevent the control device 50 from operating for a predetermined time interval (e.g., about one minute) after the antenna assembly 112 has been activated. In some embodiments, the predetermined time interval to override PWM control of the flow-control device 50 may be varied depending on setting, e.g., time and power settings, provided by the user. In some embodiments, the electrosurgical power generating source 28 may be adapted to perform a self-check routine that includes determination that the flow-control device 50 is open before enabling energy delivery between the electrosurgical power generating source 28 and the probe 100.

(81) In embodiments, features described for the electrosurgical system 10 having energy-delivery device 100 may be provided to an electrosurgical system having a handle assembly, as the handle assembly 208 shown by FIGS. 2-4. Other embodiments described herein below with reference to energy-delivery device 214 can be provided to energy-delivery device 100 of the system 10 shown by FIGS. 1A and 1B, and vice versa. Still other embodiments of the present disclosure for increasing or enhancing the ultrasonic visibility of an energy-delivery device will be described with reference to FIGS. 4-9.

(82) With reference to FIG. 4, there is shown an embodiment of the present disclosure where ultrasonic visibility of the energy-delivery device 214 of an electrosurgical system within tissue is enhanced by providing an air cavity or pocket 222 at or near the distal end 211 of the energy-delivery device 214, such as, for example, before the tip of an ablation probe (as shown in FIG. 4), RF electrode or microwave antenna. The air cavity 222 is defined by a ring groove 224. However, it is contemplated that the cavity 222 can be of any shape or configuration.

(83) With continued reference to FIG. 4, the ring groove 224 is circumferentially positioned around the energy-delivery device 214. The air cavity or pocket 222 can be created when heat shrink is placed over the top of the energy-delivery device 214. The air cavity 222 enhances ultrasonic visibility of the energy-delivery device 214 during placement, since air has a very high ultrasonic contrast compared to the surrounding tissue because of the difference in density and acoustic properties.

(84) With reference to FIG. 5, there is shown an embodiment for enhancing ultrasonic visibility of the energy-delivery device 214 within tissue by positioning a metal band 226 to the energy-delivery device 214, such as, for example, positioning a metal band, either fixedly or removably positioned, on the shaft 213 extending from the handle assembly 208, at a distal end of an ablation probe or needle. The metal band 226 can also be located between a trocar at a distal end 211 of an ablation assembly and a cooling jacket. The metal band 226 can be provided with small dimples to further enhance the ultrasonic visibility of the energy-delivery device. The metal band 226 reflects the ultrasonic waves generated during ultrasonography and thereby, increases the ultrasonic visibility of the energy-delivery device 214.

(85) With reference to FIG. 6, there is shown still another embodiment for enhancing or increasing the ultrasonic visibility of the energy-delivery device 214 within tissue. In this particular embodiment, the shape of a cooling jacket or shaft 213 of the energy-delivery device 214 is multi-sided, instead of circular, such as, for example, hexagonal. The outer surface of the cooling jacket or shaft 213 can be made multi-sided at or near the region of the radiating section of the energy-delivery device 214, such as at or near the distal end 211 of an ablation probe. The flat or substantially flat sides 228 of the cooling jacket or shaft 213 reflect the ultrasonic waves during ultrasonography, and thereby, enhance the ultrasonic visibility of the energy-delivery device 214. The surface of at least one side 228A can be made concave and/or be provided with small dimples to further enhance the ultrasonic visibility of the energy-delivery device 214.

(86) FIG. 7 illustrates a yet another embodiment of increasing or enhancing the ultrasonic visibility of the energy-delivery device 214 within tissue. In this embodiment, the cooling jacket or shaft 213 of the energy-delivery device 214 is provided with multiple metallic wires or one metallic wire which is coiled around the cooling jacket or shaft 213. The wires 230 can be individual loops or wrapped in the form of a coil or spring. The wires 230 are placed proximal to a radiating section of the energy-delivery device 214 in order to aid in identifying the start of the radiating section without interfering with the emitted energy, such as microwave energy. The wires 230 can also be placed over the active area of the radiating section in the case of an RF electrode, such as, a Cool-Tip™ electrode. The wires 230 reflect the ultrasonic waves generated during ultrasonography and thereby, increasing the ultrasonic visibility of the energy-delivery device 214.

(87) FIG. 8 shows another embodiment for enhancing the ultrasonic visibility of the energy-delivery device 214 within tissue. In this embodiment, ultrasonic visibility is enhanced by utilizing an inflatable balloon or air sac assembly 232. The assembly 232 includes an inflatable air sac or balloon 234 and at least one conduit 236 in fluid communication with a fluid source (not shown) for delivering and withdrawing fluid (liquid, gas, gel, etc.) to the air sac 234. The air sac 234 and the at least one conduit 236 are positioned along the shaft 213. By delivering fluid to the air sac 234, the air sac 234 inflates.

(88) The fluid is delivered to the air sac 234 via the at least one conduit 236 when ultrasonic visibility of the energy-delivery device 214 is desired. It is also contemplated that the fluid is delivered to chamber positioned within the chamber, such as an inner chamber. In one configuration, the fluid is added between a cooling jacket and an outermost heat shrink, such as a PET heat shrink, during ultrasonography.

(89) If a liquid is used as the fluid, the ultrasonic energy is absorbed and the liquid appears darker in contrast compared to surrounding tissue. If air is used as the fluid, the ultrasonic energy is reflected and the air appears brighter in contrast compared to surrounding tissue. The fluid can be added during guidance, positioning and placement of the energy-delivery device 214 within tissue, and be removed during the ablation procedure. The sac or balloon 234 can be positioned in the area proximal to a radiating section or on the radiating section of the energy-delivery device 214. The sac 234 can be in fluid communication with cooling fluid, such that the cooling fluid is used to inflate the sac 234.

(90) In an additional embodiment, ultrasonic visibility of the energy-delivery device 214 within tissue is enhanced by increasing ultrasound reflection at or near the distal end 211 of the energy-delivery device 214, such as, for example, at a trocar 238. The ultrasound reflection can be increased at the distal end 211 by creating a concave surface 240 at the distal end 211 and/or adding a plurality of dimples 242 to the surface of the distal end. Ultrasonic visibility is also increased by making the trocar 238 multi-sided.

(91) The distal end 211 can be made from ceramic material which is molded to have a concave surface and/or a plurality of dimples thereon. The concave surface and/or plurality of dimples increase the amount of ultrasonic energy which is reflected by the energy-delivery device 214, thereby enhancing its ultrasonic visibility. The dimples can also be added on a cooling jacket, shaft, heat shrink or other structure of the energy-delivery device 214.

(92) In yet another embodiment, with continued reference to FIG. 9, ultrasonic visibility of the energy-delivery device 214 within tissue is enhanced by adding micro spheres or protrusions of a hard material 244, such as, ceramic, glass, stainless steel, etc., at or near the radiating section or a distal end 211 of the energy-delivery device 214. The micro spheres or protrusions 244 can also be added on a cooling jacket, shaft, heat shrink or other structure of the energy-delivery device 214.

(93) The above-described methods and systems for enhancing ultrasonic visibility of energy-delivery devices or other components of electrosurgical systems may be used in conjunction with a variety of electrosurgical devices adapted for treating tissue. The above-described systems and methods may be suitable for a variety of uses and applications, including medical procedures, e.g., tissue ablation, resection, cautery, vascular thrombosis, treatment of cardiac arrhythmias and dysrhythmias, electrosurgery, etc.

(94) It is envisioned that various aspects and features of the embodiments shown by the various figures and/or described herein can be combined to form additional embodiments of the electrosurgical system 10. For example, probe 100 of electrosurgical system 10 can be provided with an air cavity at a distal end and/or a metal band as shown by the embodiments of FIGS. 4 and 5, respectively.

(95) Although embodiments have been described in detail with reference to the accompanying drawings for the purpose of illustration and description, it is to be understood that the inventive processes and apparatus are not to be construed as limited thereby. It will be apparent to those of ordinary skill in the art that various modifications to the foregoing embodiments may be made without departing from the scope of the disclosure.