US20180296266A1 - System and method for monitoring ablation size - Google Patents
System and method for monitoring ablation size Download PDFInfo
- Publication number
- US20180296266A1 US20180296266A1 US16/018,855 US201816018855A US2018296266A1 US 20180296266 A1 US20180296266 A1 US 20180296266A1 US 201816018855 A US201816018855 A US 201816018855A US 2018296266 A1 US2018296266 A1 US 2018296266A1
- Authority
- US
- United States
- Prior art keywords
- complex impedance
- electrosurgical energy
- tissue
- power
- microwave antenna
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Abandoned
Links
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
- A61B18/1815—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using microwaves
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/1206—Generators therefor
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00005—Cooling or heating of the probe or tissue immediately surrounding the probe
- A61B2018/00011—Cooling or heating of the probe or tissue immediately surrounding the probe with fluids
- A61B2018/00023—Cooling or heating of the probe or tissue immediately surrounding the probe with fluids closed, i.e. without wound contact by the fluid
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00636—Sensing and controlling the application of energy
- A61B2018/00684—Sensing and controlling the application of energy using lookup tables
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00636—Sensing and controlling the application of energy
- A61B2018/00696—Controlled or regulated parameters
- A61B2018/00702—Power or energy
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00636—Sensing and controlling the application of energy
- A61B2018/00773—Sensed parameters
- A61B2018/00875—Resistance or impedance
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/02—Radiation therapy using microwaves
- A61N5/04—Radiators for near-field treatment
- A61N5/045—Radiators for near-field treatment specially adapted for treatment inside the body
Definitions
- the present disclosure relates to systems and methods that may be used in tissue ablation procedures. More particularly, the present disclosure relates to systems and methods for monitoring ablation size during tissue ablation procedures in real-time.
- Microwave ablation procedures e.g., such as those performed for menorrhagia, are typically done to ablate the targeted tissue to denature or kill the tissue.
- Many procedures and types of devices utilizing electromagnetic radiation therapy are known in the art.
- Such microwave therapy is typically used in the treatment of tissue and organs such as the prostate, heart, and liver.
- One non-invasive procedure generally involves the treatment of tissue (e.g., a tumor) underlying the skin via the use of microwave energy.
- tissue e.g., a tumor
- the microwave energy is able to non-invasively penetrate the skin to reach the underlying tissue.
- this non-invasive procedure may result in the unwanted heating of healthy tissue.
- the non-invasive use of microwave energy requires a great deal of control.
- one or more types of sensors are operably associated with the microwave ablation device.
- a microwave ablation device that includes a monopole antenna configuration
- an elongated microwave conductor may be in operative communication with a sensor exposed at an end of the microwave conductor. This type of sensor is sometimes surrounded by a dielectric sleeve.
- the foregoing types of sensor(s) are configured to function (e.g., provide feedback to a controller for controlling the power output of a power source) when the microwave ablation device is inactive, i.e., not radiating. That is, the foregoing sensors do not function in real-time.
- the power source is powered off (or pulsed off) when the sensors are providing feedback (e.g., tissue temperature) to the controller and/or other device(s) configured to control the power source.
- the present disclosure provides a system for monitoring ablation size in real-time.
- the system includes a power source including a microprocessor for executing at least one control algorithm.
- the system includes a microwave antenna configured to deliver microwave energy from the power source to tissue forming an ablation zone.
- An ablation zone control module is in operative communication with a memory associated with the power source.
- the memory includes one or more data look-up tables including one or more electrical parameters associated with the microwave antenna. The electrical parameter(s) corresponding to a radius of the ablation zone, wherein the ablation zone control module triggers a signal when a predetermined threshold value of the electrical parameter(s) is measured corresponding to the radius of the ablation zone.
- the present disclosure provides a microwave antenna adapted to connect to a power source configured for performing an ablation procedure.
- the microwave antenna includes a radiating section configured to deliver microwave energy from a power source to tissue to form an ablation zone.
- An ablation zone control module is in operative communication with a memory associated with the power source.
- the memory includes one or more data look-up tables including one or more electrical parameters associated with the microwave antenna. The electrical parameter(s) corresponding to a radius of the ablation zone, wherein the ablation zone control module triggers a signal when a predetermined threshold value of the electrical parameter(s) is measured corresponding to the radius of the ablation zone.
- the present disclosure also provides a method for indirectly monitoring temperature of tissue undergoing ablation by way of probe impedance.
- the method includes an initial step of transmitting microwave energy from a power source to a microwave antenna to form a tissue ablation zone.
- a step of the method includes monitoring complex impedance associated with the microwave antenna as the tissue ablation zone forms.
- a step of the method includes communicating a control signal to the power source when a predetermined complex impedance is reached at the microwave antenna. Adjusting the amount of microwave energy from the power source to the microwave antenna is another step of the method.
- FIG. 1 is a perspective view of a system for monitoring ablation size according to an embodiment of the present disclosure
- FIG. 2 is a functional block diagram of a power source for use with the system depicted in FIG. 1 ;
- FIG. 3A is a schematic, plan view of the tip of a microwave antenna depicted in FIG. 2A illustrating radial ablation zones having a spherical configuration
- FIG. 3B is a schematic, plan view of the tip of a microwave antenna depicted in FIG. 1 illustrating radial ablation zones having an ellipsoidal configuration
- FIG. 4A-1 is a graphical representation of a real impedance (Zr) versus time (t) curve
- FIG. 4A-2 a graphical representation of a corresponding ablation radii (Ar) versus time (t) curve
- FIG. 4B-1 is a graphical representation of the imaginary impedance (Zi) versus time (t) curve
- FIG. 4B-2 is a graphical representation of corresponding ablation radii (Ar) versus time (t) curve.
- FIG. 5 is a flow chart illustrating a method for monitoring temperature of tissue undergoing ablation in accordance with the present disclosure.
- distal refers to the portion which is furthest from the user and the term “proximal” refers to the portion that is closest to the user.
- proximal refers to the portion that is closest to the user.
- terms such as “above”, “below”, “forward”, “rearward”, etc. refer to the orientation of the figures or the direction of components and are simply used for convenience of description.
- microwave antenna 100 that is adapted to connect to an electrosurgical power source, e.g., an RF and/or microwave (MW) generator 200 that includes or is in operative communication with one or more controllers 300 and, in some instances, a fluid supply pump 40 .
- microwave antenna 100 includes an introducer 116 having an elongated shaft 112 and a radiating or conductive section or tip 114 operably disposed within elongated shaft 112 , a cooling assembly 120 having a cooling sheath 121 , a handle 118 , a cooling fluid supply 122 and a cooling fluid return 124 , and an electrosurgical energy connector 126 .
- Connector 126 is configured to connect the microwave antenna 100 to the electrosurgical power source 200 , e.g., a generator or source of radio frequency energy and/or microwave energy, and supplies electrosurgical energy to the distal portion of the microwave antenna 100 .
- Conductive tip 114 and elongated shaft 112 are in electrical communication with connector 126 via an internal coaxial cable 126 a that extends from the proximal end of the microwave antenna 100 and includes an inner conductor tip that is operatively coupled to a radiating section 138 operably disposed within the shaft 112 and adjacent the conductive or radiating tip 114 (see FIG. 3A , for example).
- internal coaxial cable 126 a includes a dielectric material and an outer conductor surrounding each of the inner conductor tip and dielectric material.
- a connection hub (not shown) disposed at a proximal end of the microwave antenna 100 operably couples connector 126 to internal coaxial cable 126 a , and cooling fluid supply 122 and a cooling fluid return 124 to a cooling assembly 120 .
- Radiating section 138 by way of conductive tip 114 is configured to deliver radio frequency energy (in either a bipolar or monopolar mode) or microwave energy (having a frequency of about 500 MHz to about 10 GHz) to a target tissue site.
- Elongated shaft 112 and conductive tip 114 may be formed of suitable conductive material including, but not limited to copper, gold, silver or other conductive metals having similar conductivity values.
- elongated shaft 112 and/or conductive tip 114 may be constructed from stainless steel or may be plated with other materials, e.g., other conductive materials, such as gold or silver, to improve certain properties, e.g., to improve conductivity, decrease energy loss, etc.
- the conductive tip may be deployable from the elongated shaft 112 .
- the generator 200 includes a controller 300 having one or more modules (e.g., an ablation zone control module 332 (AZCM 332 ), a power supply 237 and a microwave output stage 238 ).
- generator 200 is described with respect to the delivery of microwave energy.
- the power supply 237 provides DC power to the microwave output stage 238 which then converts the DC power into microwave energy and delivers the microwave energy to the radiating section 138 of the microwave antenna 100 .
- the controller 300 may include analog and/or logic circuitry for processing sensed values provided by the AZCM 332 and determining the control signals that are sent to the generator 200 and/or supply pump 40 via a microprocessor 335 .
- the controller 300 (or component operably associated therewith) accepts one or more measured signals indicative of calculated complex impedance associated with the microwave antenna 100 and/or tissue adjacent an ablation zone when the microwave antenna is radiating energy.
- One or more modules e.g., AZCM 332 , of the controller 300 analyzes the measured signals and determines if a threshold complex impedance has been met. If the threshold complex impedance has been met, then the AZCM 332 , a microprocessor 335 and/or the controller instructs the generator 200 to adjust the microwave output stage 238 and/or the power supply 237 accordingly. Additionally, the controller 300 may also signal the supply pump to adjust the amount of cooling fluid to the microwave antenna 100 and/or the surrounding tissue.
- the controller 200 includes microprocessor 335 having memory 336 which may be volatile type memory (e.g., RAM) and/or non-volatile type memory (e.g., flash media, disk media, etc.).
- the microprocessor 335 is in operative communication with the power supply 237 and/or microwave output stage 238 allowing the microprocessor 335 to control the output of the generator 300 according to either open and/or closed control loop schemes.
- the microprocessor 335 is capable of executing software instructions for processing data received by the AZCM 332 , and for outputting control signals to the generator 300 and/or supply pump 40 , accordingly.
- the software instructions, which are executable by the controller 300 are stored in the memory 336 .
- One or more control algorithms for predicting tissue ablation size is implemented by the controller 300 . More particularly, the concept of correlating complex impedance (e.g., real and imaginary portions of the complex impedance) associated with a particular microwave antenna, e.g., the microwave antenna 100 , with an ablation zone “A” having a radius “r” may be used to indicate tissue death or necrosis. More particularly, complex impedance associated with the microwave antenna 100 varies over the course of an ablation cycle due to tissue complex permittivity changes caused by temperature increase (see FIGS. 4A-1 and 4B-1 , for example). A relationship of complex impedance as a function of time may be represented by the curves illustrated in FIGS.
- complex impedance e.g., real and imaginary portions of the complex impedance
- the ablated tissue is in a “near field” of the microwave antenna 100 , the ablated tissue essentially becomes part of the microwave antenna 100 . Accordingly, when a dielectric constant and conductivity associated with the ablated tissue reaches a steady-state condition, the complex impedance at the microwave antenna 100 also reaches a steady-state condition, e.g., Zss, where Zss includes a real portion Zrss and an imaginary portion Ziss, see FIGS. 4A-1 and 4B-1 , respectively.
- a steady-state condition e.g., Zss, where Zss includes a real portion Zrss and an imaginary portion Ziss, see FIGS. 4A-1 and 4B-1 , respectively.
- Zss may vary for a given microwave antenna.
- Factors that may contribute to a specific Zss for a given microwave antenna include but are not limited to: dimensions associated with the microwave antenna (e.g., length, width, etc.); type of material used to manufacture the microwave antenna (or portion associated therewith, e.g., a radiating section) such as copper, silver, etc; and the configuration of the radiating section (e.g., dipole, monopole, etc.) and/or a conductive tip (e.g., sharp, blunt, curved, etc) associated with the microwave antenna.
- dimensions associated with the microwave antenna e.g., length, width, etc.
- type of material used to manufacture the microwave antenna or portion associated therewith, e.g., a radiating section
- the configuration of the radiating section e.g., dipole, monopole, etc.
- a conductive tip e.g., sharp, blunt, curved, etc
- the control algorithm implements one or more model equations and/or curves, e.g., curves depicted in FIGS. 4A-1 and 4B-1 , to calculate the Zss associated with the microwave antenna 100 within a specified time range (e.g., t1-tss) not exceeding tss, i.e., time when the ablated tissue is at the steady-state condition (see FIG. 4A-1 or FIG. 4B-1 , for example). More particularly, the real and imaginary portions, Zrss and Ziss, respectively, of the Zss of the microwave antenna 100 may be calculated via monitoring and/or measuring of a signal (or pulse) generated by the generator 200 .
- a signal or pulse
- a phase (for calculating an imaginary impedance Ziss of the complex impedance) and magnitude (for calculating a real impedance Zrss of the complex impedance) associated with a signal (or pulse) generated by the generator 200 during an ablation procedure may be sampled and monitored.
- one or more electrical properties (e.g., voltage, current, power, impedance, etc.) associated with a signal (or pulse) generated by the generator 200 may be sampled and monitored. More particularly, electrical properties associated with a forward and reflected portion of the signal generated by the generator 200 is sampled and monitored.
- forward and reflected power, Pfwd and Pref, respectively, of a signal for ablating tissue is measured by the AZCM 332 , controller 300 , microprocessor 337 or other suitable module associated with the generator 200 and/or controller 200 . Thereafter, the power standing wave ratio (Pswr) is calculated using the equation:
- Pfwd is the power associated with the generated signal (i.e., forward signal) and Pref is the power associated with the reflected signal.
- the real portion of the complex impedance at the steady-state condition, e.g., Zss, of the microwave antenna 100 may be calculated. More particularly, the phase difference between the forward and reflected power may be used to calculate the imaginary portion Ziss of the complex impedance and the magnitude difference between the forward and reflected power may be used to calculate the real portion Zrss of the complex impedance.
- Zss may be calculated and, subsequently, communicated and/or relayed to one or more modules associated with the controller 300 , e.g., AZCM 332 , to determine if a predetermined threshold value Zss that corresponds to a desired ablation size has been met.
- AZCM 332 known characteristic impedance associated with connector 126 and/or internal cable 126 a may be employed to determine Zss. More particularly, measurement of Zss may be determined using the equation:
- Zo is the characteristic impedance associated with the connector 126 and/or internal cable 126 a .
- the characteristic impedance Zo is an accurate measure of the impedance of the connector 126 and/or internal cable 126 a and takes into account the line losses associated with the connector 126 and/or internal cable 126 a . In this instance, after all the necessary calculations have been carried out, the measurement of Zss will be an accurate representation of the steady-state impedance Zss at the microwave antenna 100 adjacent the ablation zone.
- the foregoing algorithms and/or equations are two of many algorithms and/or equations that may be employed to calculate the Zss associated with the microwave antenna 100 such that real-time monitoring of an ablation zone may be achieved.
- one or more model functions ⁇ (t) representative of the model curves illustrated in FIGS. 4A-1 and 4B-1 may be utilized in conjunction with the aforementioned equations (or alone) to obtain additional information relevant to Zss. More particularly, a measurement of a slope of a tangent line at a point along either of the curves (e.g., curve illustrated in FIG. 4A-1 ) is equal to a derivative (dz/dt) of the curve at that point.
- the calculation of the derivative at a particular point along the curve(s) may provide additional information, e.g., rate of change of complex impedance with respect to time.
- This rate of change associated with complex impedance with respect to time may be utilized, for example, to determine the time it takes to go from Z4 to Zss during an ablation procedure.
- the microwave antenna 100 of the present disclosure may be configured to create an ablation zone “A” having any suitable configuration, such as, for example, spherical ( FIG. 3A ), hemispherical, ellipsoidal ( FIG. 3B where the ablation zone is designated “A-2”), and so forth.
- microwave antenna 100 is configured to create an ablation zone “A” that is spherical ( FIG. 3A ).
- a dielectric constant and conductivity associated with the ablated tissue reaches a steady-state that corresponds to a steady-state complex impedance Zss associated with the microwave antenna 100 .
- Correlating the Zss associated with the microwave antenna 100 with the ablated tissue indicates a specific size (e.g., radius rss) and shape (e.g., spherical) of the ablation zone “A.”
- a measure of Zss associated with the microwave antenna 100 corresponds to an ablation zone “A” having a radius r, e.g., rss.
- the control algorithm of the present disclosure uses known or calculated steady state complex impedances associated with specific microwave antennas at specific radii to predict an ablation size.
- complex impedances e.g., Zss
- a specific microwave antenna e.g., microwave antenna 100
- corresponding radius e.g., rss
- impedance measurements may be taken at times prior to tss, e.g., times t1-t4.
- complex impedances e.g., Z1-Z4 (for illustrative purposes and clarity, Z1-Z4 are defined by both the real and imaginary portions of the complex impedance) associated with the microwave antenna 100 may be correlated with an ablation zone “A” defined by a plurality of concentric ablation zones having radii r1-r4 (collectively referred to as radii “r”) when measured from the center of the ablation zone “A.”
- the complex impedances Z1-Z4 and corresponding radii “r” may be correlated with each other in a manner as described above with respect to Zss and rss (see FIG.
- AZCM 332 may be a separate module from the microprocessor 335 , or AZCM 332 may be included with the microprocessor 335 . In an embodiment, the AZCM 332 may be operably disposed on the microwave antenna 100 .
- the AZCM 332 may include control circuitry that receives information from one or more control modules and/or one or more impedance sensors (not shown), and provides the information to the controller 300 and/or microprocessor 335 .
- the AZCM 332 , microprocessor 335 and/or controller 300 may access look-up table “D” and confirm that a particular complex impedance (e.g., Zss) associated with microwave assembly 100 that corresponds to a specific ablation zone, e.g., specific ablation zone having a radius rss has been met and, subsequently instruct the generator 200 to adjust the amount of microwave energy being delivered to the microwave antenna.
- look-up table “D” may be stored in a memory storage device (not shown) associated with the microwave antenna 100 .
- a look-up table “D” may be stored in a memory storage device operatively associated with handle 118 and/or connector 126 of the microwave antenna 100 and may be downloaded, read and stored into microprocessor 335 and/or memory 336 and, subsequently, accessed and utilized in a manner described above; this would do away with reprogramming the generator 200 and/or controller 300 for a specific microwave antenna.
- the memory storage device may also be configured to include information pertaining to the microwave antenna 100 . For example, information such as, the type of microwave antenna, the type of tissue that the microwave antenna is configured to treat, the type of ablation zone desired, etc. may be stored into the storage device associated with the microwave antenna.
- generator 200 and/or controller 300 of system 10 may be adapted for use with a microwave antenna configured to create an ablation zone, e.g. ablation zone “A-2,” different from that of microwave antenna 100 that is configured to create an ablation zone “A.”
- the generator is shown operably coupled to fluid supply pump 40 .
- the supply pump 40 is, in turn, operably coupled to the supply tank 44 ( FIG. 2 ).
- the microprocessor 335 is in operative communication with the supply pump 40 via one or more suitable types of interfaces, e.g., a port 240 operatively disposed on the generator 200 , which allows the microprocessor 335 to control the output of a cooling fluid 42 from the supply pump 40 to the microwave antenna 100 according to either open and/or closed control loop schemes.
- the controller 300 may signal the supply pump 40 to control the output of cooling fluid 42 from the supply tank 44 to the microwave antenna 100 .
- cooling fluid 42 is automatically circulated to the microwave antenna 100 and back to the supply pump 40 .
- a clinician may manually control the supply pump 40 to cause cooling fluid 42 to be expelled from the microwave antenna 100 into and/or proximate the surrounding tissue.
- microwave antenna 100 is connected to generator 200 .
- one or more modules, e.g., AZCM 332 , associated with the generator 200 and/or controller 300 reads and/or downloads data from a storage device associated with the antenna 100 , e.g., the type of microwave antenna, the type of tissue that is to be treated, etc.
- Microwave antenna 100 may then be positioned adjacent tissue ( FIG. 3A ).
- generator 200 may be activated supplying microwave energy to radiating section 138 of the microwave antenna 100 such that the tissue may be ablated.
- the AZCM 332 instructs the generator 200 to adjust the microwave energy accordingly.
- the AZCM 332 functions in real-time controlling the amount of microwave energy to the ablation zone such that a uniform ablation zone of suitable proportion (e.g., ablation zone “A” having a radius rss) is formed with minimal or no damage to adjacent tissue.
- a uniform ablation zone of suitable proportion e.g., ablation zone “A” having a radius rss
- a method 400 for monitoring temperature of tissue undergoing ablation is illustrated.
- microwave energy from generator 200 is transmitted to a microwave antenna 100 adjacent a tissue ablation site.
- complex impedance associated with the microwave antenna is monitored.
- a detection signal is communicated to the generator 200 when a predetermined complex impedance Zss is reached at the microwave antenna 100 .
- the amount of microwave energy from the generator 200 to the microwave antenna 100 may be adjusted.
- one or more directional couplers may be operatively associated with the generator 200 , controller 300 and/or AZCM 332 , and configured to sample the forward, reflected, and/or load power portions of an output signal (or pulse) and direct the sampled signal to the AZCM 332 .
- the directional coupler provides samples of the forward and reflected signal (or pulse) generated by the generator 200 .
- the power, magnitude and phase of the generated output signal may be obtained or calculated from the measured forward and reflected signals by conventional algorithms that may employ one or both of the aforementioned equations (1) (2), or other suitable equation.
- energy values or parameters e.g., power, voltage, current, impedance, magnitude and phase
- the connector 126 and/or internal cable 126 a may include transmission line losses.
- AZCM 332 or other suitable module or component associated with the controller 300 ) may be configured to adjust and/or calibrate Zss to compensate for losses associated with connector 126 and/or internal cable 126 a .
- line loss information associated with the connector 126 and/or internal cable 126 a may be determined and stored into memory 336 and accessed during an ablation procedure by the AZCM 332 and, subsequently, used in determining if a predetermined threshold value of Zss has been met.
- loss information for connector 126 and/or internal cable 126 a may be determined and, subsequently, stored in memory 336 and accessed by one or more modules, such as, for example, a calibration module 600 or other suitable module (e.g., AZCM 332 ) for later use.
- the loss information for connector 126 and/or internal cable 126 a may be determined by any suitable device and/or method.
- the loss information for connector 126 and/or internal cable 126 a may be determined via network analyzer 602 .
- the network analyzer 602 may be an integral part of generator 200 (e.g., part of calibration module 600 ) or alternatively, the network analyzer 602 may be a separate handheld device that is in operative communication with generator 200 .
- the network analyzer 602 may be used to perform a diagnostic test of connector 126 and/or internal cable 126 a .
- the network analyzer 602 may function in a fashion similar to most conventional network analyzers that are known in the available art.
- the network analyzer 602 may determine the properties that are associated with connector 126 and/or internal cable 126 a , and more particularly, those properties that are associated with connector 126 and/or internal cable 126 a that affect the reflection and/or transmission of an output signal, such as, for example, the characteristic impedance Zo of connector 126 and/or internal cable 126 a .
- the network analyzer 602 may be narrow band or single frequency, e.g., microwave frequency utilized by system 10 , which, in turn, may reduce the complexity of the system 10 .
- control algorithm of the present disclosure implements one or more model equations and/or curves to calculate Zss within the time range t1-tss.
- system 10 and operative components associated therewith e.g., AZCM 332 , may be configured to monitor ablation zone size after time tss. More particularly, system 10 may be configured to deliver “x” amount of electrosurgical energy to microwave antenna 100 for “n” more seconds such that an ablation zone “A” having a radius “y” is achieved.
Landscapes
- Health & Medical Sciences (AREA)
- Surgery (AREA)
- Life Sciences & Earth Sciences (AREA)
- Biomedical Technology (AREA)
- Medical Informatics (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Electromagnetism (AREA)
- Engineering & Computer Science (AREA)
- Physics & Mathematics (AREA)
- Heart & Thoracic Surgery (AREA)
- Otolaryngology (AREA)
- Molecular Biology (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Surgical Instruments (AREA)
Abstract
Description
- The present application is a continuation application of U.S. patent application Ser. No. 14/532,317 filed Nov. 4, 2014, now U.S. patent Ser. No. 10/004,559, which is a continuation application of U.S. patent application Ser. No. 14/064,846 filed Oct. 28, 2013, now U.S. Pat. No. 8,894,641, which is a divisional application of U.S. patent application Ser. No. 12/606,769 filed on Oct. 27, 2009, now U.S. Pat. No. 8,568,401, the entire contents of each of which are incorporated herein by reference.
- The present disclosure relates to systems and methods that may be used in tissue ablation procedures. More particularly, the present disclosure relates to systems and methods for monitoring ablation size during tissue ablation procedures in real-time.
- In the treatment of diseases such as cancer, certain types of cancer cells have been found to denature at elevated temperatures (which are slightly lower than temperatures normally injurious to healthy cells). These types of treatments, known generally as hyperthermia therapy, typically utilize electromagnetic radiation to heat diseased cells to temperatures above 41° C. while maintaining adjacent healthy cells at lower temperatures where irreversible cell destruction will not occur. Procedures utilizing electromagnetic radiation to heat tissue may include ablation of the tissue.
- Microwave ablation procedures, e.g., such as those performed for menorrhagia, are typically done to ablate the targeted tissue to denature or kill the tissue. Many procedures and types of devices utilizing electromagnetic radiation therapy are known in the art. Such microwave therapy is typically used in the treatment of tissue and organs such as the prostate, heart, and liver.
- One non-invasive procedure generally involves the treatment of tissue (e.g., a tumor) underlying the skin via the use of microwave energy. The microwave energy is able to non-invasively penetrate the skin to reach the underlying tissue. However, this non-invasive procedure may result in the unwanted heating of healthy tissue. Thus, the non-invasive use of microwave energy requires a great deal of control.
- Currently, there are several types of systems and methods for monitoring ablation zone size. In certain instances, one or more types of sensors (or other suitable devices) are operably associated with the microwave ablation device. For example, in a microwave ablation device that includes a monopole antenna configuration, an elongated microwave conductor may be in operative communication with a sensor exposed at an end of the microwave conductor. This type of sensor is sometimes surrounded by a dielectric sleeve.
- Typically, the foregoing types of sensor(s) are configured to function (e.g., provide feedback to a controller for controlling the power output of a power source) when the microwave ablation device is inactive, i.e., not radiating. That is, the foregoing sensors do not function in real-time. Typically, the power source is powered off (or pulsed off) when the sensors are providing feedback (e.g., tissue temperature) to the controller and/or other device(s) configured to control the power source.
- The present disclosure provides a system for monitoring ablation size in real-time. The system includes a power source including a microprocessor for executing at least one control algorithm. The system includes a microwave antenna configured to deliver microwave energy from the power source to tissue forming an ablation zone. An ablation zone control module is in operative communication with a memory associated with the power source. The memory includes one or more data look-up tables including one or more electrical parameters associated with the microwave antenna. The electrical parameter(s) corresponding to a radius of the ablation zone, wherein the ablation zone control module triggers a signal when a predetermined threshold value of the electrical parameter(s) is measured corresponding to the radius of the ablation zone.
- The present disclosure provides a microwave antenna adapted to connect to a power source configured for performing an ablation procedure. The microwave antenna includes a radiating section configured to deliver microwave energy from a power source to tissue to form an ablation zone. An ablation zone control module is in operative communication with a memory associated with the power source. The memory includes one or more data look-up tables including one or more electrical parameters associated with the microwave antenna. The electrical parameter(s) corresponding to a radius of the ablation zone, wherein the ablation zone control module triggers a signal when a predetermined threshold value of the electrical parameter(s) is measured corresponding to the radius of the ablation zone.
- The present disclosure also provides a method for indirectly monitoring temperature of tissue undergoing ablation by way of probe impedance. The method includes an initial step of transmitting microwave energy from a power source to a microwave antenna to form a tissue ablation zone. A step of the method includes monitoring complex impedance associated with the microwave antenna as the tissue ablation zone forms. A step of the method includes communicating a control signal to the power source when a predetermined complex impedance is reached at the microwave antenna. Adjusting the amount of microwave energy from the power source to the microwave antenna is another step of the method.
- The above and other aspects, features, and advantages of the present disclosure will become more apparent in light of the following detailed description when taken in conjunction with the accompanying drawings in which:
-
FIG. 1 is a perspective view of a system for monitoring ablation size according to an embodiment of the present disclosure; -
FIG. 2 is a functional block diagram of a power source for use with the system depicted inFIG. 1 ; -
FIG. 3A is a schematic, plan view of the tip of a microwave antenna depicted inFIG. 2A illustrating radial ablation zones having a spherical configuration; -
FIG. 3B is a schematic, plan view of the tip of a microwave antenna depicted inFIG. 1 illustrating radial ablation zones having an ellipsoidal configuration; -
FIG. 4A-1 is a graphical representation of a real impedance (Zr) versus time (t) curve; -
FIG. 4A-2 a graphical representation of a corresponding ablation radii (Ar) versus time (t) curve; -
FIG. 4B-1 is a graphical representation of the imaginary impedance (Zi) versus time (t) curve; -
FIG. 4B-2 is a graphical representation of corresponding ablation radii (Ar) versus time (t) curve; and -
FIG. 5 is a flow chart illustrating a method for monitoring temperature of tissue undergoing ablation in accordance with the present disclosure. - Embodiments of the presently disclosed system and method are described in detail with reference to the drawing figures wherein like reference numerals identify similar or identical elements. As used herein and as is traditional, the term “distal” refers to the portion which is furthest from the user and the term “proximal” refers to the portion that is closest to the user. In addition, terms such as “above”, “below”, “forward”, “rearward”, etc. refer to the orientation of the figures or the direction of components and are simply used for convenience of description.
- Referring now to
FIG. 1 , a system for monitoring ablation size is designated 10. Thesystem 10 includes amicrowave antenna 100 that is adapted to connect to an electrosurgical power source, e.g., an RF and/or microwave (MW)generator 200 that includes or is in operative communication with one ormore controllers 300 and, in some instances, afluid supply pump 40. Briefly,microwave antenna 100 includes anintroducer 116 having anelongated shaft 112 and a radiating or conductive section ortip 114 operably disposed withinelongated shaft 112, a coolingassembly 120 having a cooling sheath 121, ahandle 118, a coolingfluid supply 122 and a coolingfluid return 124, and anelectrosurgical energy connector 126.Connector 126 is configured to connect themicrowave antenna 100 to theelectrosurgical power source 200, e.g., a generator or source of radio frequency energy and/or microwave energy, and supplies electrosurgical energy to the distal portion of themicrowave antenna 100.Conductive tip 114 andelongated shaft 112 are in electrical communication withconnector 126 via an internalcoaxial cable 126 a that extends from the proximal end of themicrowave antenna 100 and includes an inner conductor tip that is operatively coupled to aradiating section 138 operably disposed within theshaft 112 and adjacent the conductive or radiating tip 114 (seeFIG. 3A , for example). As is common in the art, internalcoaxial cable 126 a includes a dielectric material and an outer conductor surrounding each of the inner conductor tip and dielectric material. A connection hub (not shown) disposed at a proximal end of themicrowave antenna 100operably couples connector 126 to internalcoaxial cable 126 a, and coolingfluid supply 122 and a coolingfluid return 124 to acooling assembly 120.Radiating section 138 by way of conductive tip 114 (or in certain instances without conductive tip 114) is configured to deliver radio frequency energy (in either a bipolar or monopolar mode) or microwave energy (having a frequency of about 500 MHz to about 10 GHz) to a target tissue site.Elongated shaft 112 andconductive tip 114 may be formed of suitable conductive material including, but not limited to copper, gold, silver or other conductive metals having similar conductivity values. Alternatively,elongated shaft 112 and/orconductive tip 114 may be constructed from stainless steel or may be plated with other materials, e.g., other conductive materials, such as gold or silver, to improve certain properties, e.g., to improve conductivity, decrease energy loss, etc. In an embodiment, the conductive tip may be deployable from theelongated shaft 112. - With reference to
FIG. 2 , a schematic block diagram of thegenerator 200 is illustrated. Thegenerator 200 includes acontroller 300 having one or more modules (e.g., an ablation zone control module 332 (AZCM 332), apower supply 237 and a microwave output stage 238). In this instance,generator 200 is described with respect to the delivery of microwave energy. Thepower supply 237 provides DC power to themicrowave output stage 238 which then converts the DC power into microwave energy and delivers the microwave energy to theradiating section 138 of themicrowave antenna 100. Thecontroller 300 may include analog and/or logic circuitry for processing sensed values provided by theAZCM 332 and determining the control signals that are sent to thegenerator 200 and/orsupply pump 40 via amicroprocessor 335. The controller 300 (or component operably associated therewith) accepts one or more measured signals indicative of calculated complex impedance associated with themicrowave antenna 100 and/or tissue adjacent an ablation zone when the microwave antenna is radiating energy. - One or more modules e.g.,
AZCM 332, of thecontroller 300 analyzes the measured signals and determines if a threshold complex impedance has been met. If the threshold complex impedance has been met, then theAZCM 332, amicroprocessor 335 and/or the controller instructs thegenerator 200 to adjust themicrowave output stage 238 and/or thepower supply 237 accordingly. Additionally, thecontroller 300 may also signal the supply pump to adjust the amount of cooling fluid to themicrowave antenna 100 and/or the surrounding tissue. Thecontroller 200 includesmicroprocessor 335 havingmemory 336 which may be volatile type memory (e.g., RAM) and/or non-volatile type memory (e.g., flash media, disk media, etc.). In the illustrated embodiment, themicroprocessor 335 is in operative communication with thepower supply 237 and/ormicrowave output stage 238 allowing themicroprocessor 335 to control the output of thegenerator 300 according to either open and/or closed control loop schemes. Themicroprocessor 335 is capable of executing software instructions for processing data received by theAZCM 332, and for outputting control signals to thegenerator 300 and/orsupply pump 40, accordingly. The software instructions, which are executable by thecontroller 300, are stored in thememory 336. - One or more control algorithms for predicting tissue ablation size is implemented by the
controller 300. More particularly, the concept of correlating complex impedance (e.g., real and imaginary portions of the complex impedance) associated with a particular microwave antenna, e.g., themicrowave antenna 100, with an ablation zone “A” having a radius “r” may be used to indicate tissue death or necrosis. More particularly, complex impedance associated with themicrowave antenna 100 varies over the course of an ablation cycle due to tissue complex permittivity changes caused by temperature increase (seeFIGS. 4A-1 and 4B-1 , for example). A relationship of complex impedance as a function of time may be represented by the curves illustrated inFIGS. 4A-1 (real portion of complex impedance) and 4B-1 (imaginary portion of complex impedance). When themicrowave antenna 100 has heated tissue to a maximum attainable temperature, an ablation zone “A” having a corresponding radius “r” (e.g., rss) is formed (seeFIG. 3A in combination withFIGS. 4A-2 and 4B-2 , for example). At this maximum temperature a dielectric constant and conductivity associated with the ablated tissue reach a steady-state condition (this steady-state condition occurs at time tss) that corresponds to a steady-state complex impedance Zss (hereinafter referred to simply as Zss) associated with themicrowave antenna 100. That is, because the ablated tissue is in a “near field” of themicrowave antenna 100, the ablated tissue essentially becomes part of themicrowave antenna 100. Accordingly, when a dielectric constant and conductivity associated with the ablated tissue reaches a steady-state condition, the complex impedance at themicrowave antenna 100 also reaches a steady-state condition, e.g., Zss, where Zss includes a real portion Zrss and an imaginary portion Ziss, seeFIGS. 4A-1 and 4B-1 , respectively. - It should be noted, that Zss may vary for a given microwave antenna. Factors that may contribute to a specific Zss for a given microwave antenna include but are not limited to: dimensions associated with the microwave antenna (e.g., length, width, etc.); type of material used to manufacture the microwave antenna (or portion associated therewith, e.g., a radiating section) such as copper, silver, etc; and the configuration of the radiating section (e.g., dipole, monopole, etc.) and/or a conductive tip (e.g., sharp, blunt, curved, etc) associated with the microwave antenna.
- The control algorithm implements one or more model equations and/or curves, e.g., curves depicted in
FIGS. 4A-1 and 4B-1 , to calculate the Zss associated with themicrowave antenna 100 within a specified time range (e.g., t1-tss) not exceeding tss, i.e., time when the ablated tissue is at the steady-state condition (seeFIG. 4A-1 orFIG. 4B-1 , for example). More particularly, the real and imaginary portions, Zrss and Ziss, respectively, of the Zss of themicrowave antenna 100 may be calculated via monitoring and/or measuring of a signal (or pulse) generated by thegenerator 200. More particularly, a phase (for calculating an imaginary impedance Ziss of the complex impedance) and magnitude (for calculating a real impedance Zrss of the complex impedance) associated with a signal (or pulse) generated by thegenerator 200 during an ablation procedure may be sampled and monitored. For example, one or more electrical properties (e.g., voltage, current, power, impedance, etc.) associated with a signal (or pulse) generated by thegenerator 200 may be sampled and monitored. More particularly, electrical properties associated with a forward and reflected portion of the signal generated by thegenerator 200 is sampled and monitored. For example, in one particular embodiment, forward and reflected power, Pfwd and Pref, respectively, of a signal for ablating tissue is measured by theAZCM 332,controller 300, microprocessor 337 or other suitable module associated with thegenerator 200 and/orcontroller 200. Thereafter, the power standing wave ratio (Pswr) is calculated using the equation: -
- where Pfwd is the power associated with the generated signal (i.e., forward signal) and Pref is the power associated with the reflected signal. Those skilled in the relative art can appreciate that with the Pswr, Pfwd and Pref calculated the real portion of the complex impedance at the steady-state condition, e.g., Zss, of the
microwave antenna 100 may be calculated. More particularly, the phase difference between the forward and reflected power may be used to calculate the imaginary portion Ziss of the complex impedance and the magnitude difference between the forward and reflected power may be used to calculate the real portion Zrss of the complex impedance. With Zrss and Ziss known, Zss may be calculated and, subsequently, communicated and/or relayed to one or more modules associated with thecontroller 300, e.g.,AZCM 332, to determine if a predetermined threshold value Zss that corresponds to a desired ablation size has been met. For example, in certain instances, known characteristic impedance associated withconnector 126 and/orinternal cable 126 a may be employed to determine Zss. More particularly, measurement of Zss may be determined using the equation: -
- where, Zo is the characteristic impedance associated with the
connector 126 and/orinternal cable 126 a. The characteristic impedance Zo is an accurate measure of the impedance of theconnector 126 and/orinternal cable 126 a and takes into account the line losses associated with theconnector 126 and/orinternal cable 126 a. In this instance, after all the necessary calculations have been carried out, the measurement of Zss will be an accurate representation of the steady-state impedance Zss at themicrowave antenna 100 adjacent the ablation zone. - The foregoing algorithms and/or equations are two of many algorithms and/or equations that may be employed to calculate the Zss associated with the
microwave antenna 100 such that real-time monitoring of an ablation zone may be achieved. For example, one or more model functions ƒ(t) representative of the model curves illustrated inFIGS. 4A-1 and 4B-1 may be utilized in conjunction with the aforementioned equations (or alone) to obtain additional information relevant to Zss. More particularly, a measurement of a slope of a tangent line at a point along either of the curves (e.g., curve illustrated inFIG. 4A-1 ) is equal to a derivative (dz/dt) of the curve at that point. The calculation of the derivative at a particular point along the curve(s) may provide additional information, e.g., rate of change of complex impedance with respect to time. This rate of change associated with complex impedance with respect to time may be utilized, for example, to determine the time it takes to go from Z4 to Zss during an ablation procedure. - The
microwave antenna 100 of the present disclosure may be configured to create an ablation zone “A” having any suitable configuration, such as, for example, spherical (FIG. 3A ), hemispherical, ellipsoidal (FIG. 3B where the ablation zone is designated “A-2”), and so forth. In one particular embodiment,microwave antenna 100 is configured to create an ablation zone “A” that is spherical (FIG. 3A ). As noted above, when themicrowave antenna 100 has heated tissue in the “near field” to a maximum temperature, a dielectric constant and conductivity associated with the ablated tissue reaches a steady-state that corresponds to a steady-state complex impedance Zss associated with themicrowave antenna 100. Correlating the Zss associated with themicrowave antenna 100 with the ablated tissue (i.e., ablated tissue, where the dielectric constant and conductivity are in a steady-state condition), indicates a specific size (e.g., radius rss) and shape (e.g., spherical) of the ablation zone “A.” Thus, a measure of Zss associated with themicrowave antenna 100 corresponds to an ablation zone “A” having a radius r, e.g., rss. The control algorithm of the present disclosure uses known or calculated steady state complex impedances associated with specific microwave antennas at specific radii to predict an ablation size. That is, complex impedances, e.g., Zss, associated with a specific microwave antenna, e.g.,microwave antenna 100, and corresponding radius, e.g., rss, are compiled into one or more look-up tables “D” and are stored in memory, e.g.,memory 336, accessible by themicroprocessor 335 and/or theAZCM 332. Thus, when the complex impedance for a specific microwave antenna, e.g.,microwave antenna 100, reaches Zss one or more modules,e.g. AZCM 332, associated with thecontroller 300, commands thecontroller 200 to adjust the power output to themicrowave antenna 100 accordingly. This combination of events will provide an ablation zone “A” with a radius approximately equal to rss. - In an embodiment, for a given microwave antenna, e.g.,
microwave antenna 100, impedance measurements may be taken at times prior to tss, e.g., times t1-t4. In this instance, complex impedances, e.g., Z1-Z4 (for illustrative purposes and clarity, Z1-Z4 are defined by both the real and imaginary portions of the complex impedance), associated with themicrowave antenna 100 may be correlated with an ablation zone “A” defined by a plurality of concentric ablation zones having radii r1-r4 (collectively referred to as radii “r”) when measured from the center of the ablation zone “A.” More particularly, the complex impedances Z1-Z4 and corresponding radii “r” may be correlated with each other in a manner as described above with respect to Zss and rss (seeFIG. 3A in combination withFIGS. 4A-1 and 4B-1 , for example). In this instance, when specific complex impedance, e.g., Z3, is met one or more modules,e.g. AZCM 332, associated with thecontroller 300, commands thecontroller 200 to adjust the power output to themicrowave antenna 100 accordingly. -
AZCM 332 may be a separate module from themicroprocessor 335, orAZCM 332 may be included with themicroprocessor 335. In an embodiment, theAZCM 332 may be operably disposed on themicrowave antenna 100. TheAZCM 332 may include control circuitry that receives information from one or more control modules and/or one or more impedance sensors (not shown), and provides the information to thecontroller 300 and/ormicroprocessor 335. In this instance, theAZCM 332,microprocessor 335 and/orcontroller 300 may access look-up table “D” and confirm that a particular complex impedance (e.g., Zss) associated withmicrowave assembly 100 that corresponds to a specific ablation zone, e.g., specific ablation zone having a radius rss has been met and, subsequently instruct thegenerator 200 to adjust the amount of microwave energy being delivered to the microwave antenna. In one particular embodiment, look-up table “D” may be stored in a memory storage device (not shown) associated with themicrowave antenna 100. More particularly, a look-up table “D” may be stored in a memory storage device operatively associated withhandle 118 and/orconnector 126 of themicrowave antenna 100 and may be downloaded, read and stored intomicroprocessor 335 and/ormemory 336 and, subsequently, accessed and utilized in a manner described above; this would do away with reprogramming thegenerator 200 and/orcontroller 300 for a specific microwave antenna. The memory storage device may also be configured to include information pertaining to themicrowave antenna 100. For example, information such as, the type of microwave antenna, the type of tissue that the microwave antenna is configured to treat, the type of ablation zone desired, etc. may be stored into the storage device associated with the microwave antenna. In this instance, for example,generator 200 and/orcontroller 300 ofsystem 10 may be adapted for use with a microwave antenna configured to create an ablation zone, e.g. ablation zone “A-2,” different from that ofmicrowave antenna 100 that is configured to create an ablation zone “A.” - In the embodiment illustrated in
FIG. 1 , the generator is shown operably coupled tofluid supply pump 40. Thesupply pump 40 is, in turn, operably coupled to the supply tank 44 (FIG. 2 ). In embodiments, themicroprocessor 335 is in operative communication with thesupply pump 40 via one or more suitable types of interfaces, e.g., aport 240 operatively disposed on thegenerator 200, which allows themicroprocessor 335 to control the output of a coolingfluid 42 from thesupply pump 40 to themicrowave antenna 100 according to either open and/or closed control loop schemes. Thecontroller 300 may signal thesupply pump 40 to control the output of cooling fluid 42 from thesupply tank 44 to themicrowave antenna 100. In this way, coolingfluid 42 is automatically circulated to themicrowave antenna 100 and back to thesupply pump 40. In certain embodiments, a clinician may manually control thesupply pump 40 to cause coolingfluid 42 to be expelled from themicrowave antenna 100 into and/or proximate the surrounding tissue. - Operation of
system 10 is now described. In the description that follows, it is assumed that the losses associated with theconnector 126 and/or cable 162 a of themicrowave antenna 100 are negligible and thus, are not needed in calculating and/or determining a complex impedance of themicrowave antenna 100 adjacent the ablation zone during the ablation procedure. Alternatively, the losses associated with theconnector 126 and/or cable 162 a of themicrowave antenna 100 may be calibrated out of measurement (or other suitable methods) and utilized in calculating and/or determining a complex impedance of themicrowave antenna 100 adjacent the ablation zone during the ablation procedure. Initially,microwave antenna 100 is connected togenerator 200. In one particular embodiment, one or more modules, e.g.,AZCM 332, associated with thegenerator 200 and/orcontroller 300 reads and/or downloads data from a storage device associated with theantenna 100, e.g., the type of microwave antenna, the type of tissue that is to be treated, etc.Microwave antenna 100 may then be positioned adjacent tissue (FIG. 3A ). Thereafter,generator 200 may be activated supplying microwave energy to radiatingsection 138 of themicrowave antenna 100 such that the tissue may be ablated. During tissue ablation, when a predetermined complex impedance, e.g., Zss, at themicrowave antenna 100 is reached, theAZCM 332 instructs thegenerator 200 to adjust the microwave energy accordingly. In the foregoing sequence of events theAZCM 332 functions in real-time controlling the amount of microwave energy to the ablation zone such that a uniform ablation zone of suitable proportion (e.g., ablation zone “A” having a radius rss) is formed with minimal or no damage to adjacent tissue. - With reference to
FIG. 5 amethod 400 for monitoring temperature of tissue undergoing ablation is illustrated. Atstep 402, microwave energy fromgenerator 200 is transmitted to amicrowave antenna 100 adjacent a tissue ablation site. At step, 404, complex impedance associated with the microwave antenna is monitored. Atstep 406, a detection signal is communicated to thegenerator 200 when a predetermined complex impedance Zss is reached at themicrowave antenna 100. Atstep 408, the amount of microwave energy from thegenerator 200 to themicrowave antenna 100 may be adjusted. - From the foregoing and with reference to the various figure drawings, those skilled in the art will appreciate that certain modifications can also be made to the present disclosure without departing from the scope of the same. For example, one or more directional couplers (not shown) may be operatively associated with the
generator 200,controller 300 and/orAZCM 332, and configured to sample the forward, reflected, and/or load power portions of an output signal (or pulse) and direct the sampled signal to theAZCM 332. More particularly, the directional coupler provides samples of the forward and reflected signal (or pulse) generated by thegenerator 200. The power, magnitude and phase of the generated output signal may be obtained or calculated from the measured forward and reflected signals by conventional algorithms that may employ one or both of the aforementioned equations (1) (2), or other suitable equation. - It should be noted that energy values or parameters (e.g., power, voltage, current, impedance, magnitude and phase) of an output pulse are valid at the output of
generator 200. That is, theconnector 126 and/orinternal cable 126 a may include transmission line losses. In order to get a more accurate reading and/or measurement of the energy values or parameters that are delivered to themicrowave antenna 100 and/or reflected back to thegenerator 200, one would have to know the actual transmission line losses associated withconnector 126 and/orinternal cable 126 a. Accordingly, in some instances, AZCM 332 (or other suitable module or component associated with the controller 300) may be configured to adjust and/or calibrate Zss to compensate for losses associated withconnector 126 and/orinternal cable 126 a. For example, line loss information associated with theconnector 126 and/orinternal cable 126 a may be determined and stored intomemory 336 and accessed during an ablation procedure by theAZCM 332 and, subsequently, used in determining if a predetermined threshold value of Zss has been met. Thus, in an embodiment, loss information forconnector 126 and/orinternal cable 126 a may be determined and, subsequently, stored inmemory 336 and accessed by one or more modules, such as, for example, acalibration module 600 or other suitable module (e.g., AZCM 332) for later use. The loss information forconnector 126 and/orinternal cable 126 a may be determined by any suitable device and/or method. For example, the loss information forconnector 126 and/orinternal cable 126 a may be determined vianetwork analyzer 602. In one particular embodiment, thenetwork analyzer 602 may be an integral part of generator 200 (e.g., part of calibration module 600) or alternatively, thenetwork analyzer 602 may be a separate handheld device that is in operative communication withgenerator 200. Thenetwork analyzer 602 may be used to perform a diagnostic test ofconnector 126 and/orinternal cable 126 a. Thenetwork analyzer 602 may function in a fashion similar to most conventional network analyzers that are known in the available art. That is, thenetwork analyzer 602 may determine the properties that are associated withconnector 126 and/orinternal cable 126 a, and more particularly, those properties that are associated withconnector 126 and/orinternal cable 126 a that affect the reflection and/or transmission of an output signal, such as, for example, the characteristic impedance Zo ofconnector 126 and/orinternal cable 126 a. In embodiments, thenetwork analyzer 602 may be narrow band or single frequency, e.g., microwave frequency utilized bysystem 10, which, in turn, may reduce the complexity of thesystem 10. - As noted above, the control algorithm of the present disclosure implements one or more model equations and/or curves to calculate Zss within the time range t1-tss. In certain instances, however, for a particular probe,
system 10 and operative components associated therewith, e.g.,AZCM 332, may be configured to monitor ablation zone size after time tss. More particularly,system 10 may be configured to deliver “x” amount of electrosurgical energy tomicrowave antenna 100 for “n” more seconds such that an ablation zone “A” having a radius “y” is achieved. - While several embodiments of the disclosure have been shown in the drawings and/or discussed herein, it is not intended that the disclosure be limited thereto, as it is intended that the disclosure be as broad in scope as the art will allow and that the specification be read likewise. Therefore, the above description should not be construed as limiting, but merely as exemplifications of particular embodiments. Those skilled in the art will envision other modifications within the scope and spirit of the claims appended hereto.
Claims (21)
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US16/018,855 US20180296266A1 (en) | 2009-10-27 | 2018-06-26 | System and method for monitoring ablation size |
Applications Claiming Priority (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US12/606,769 US8568401B2 (en) | 2009-10-27 | 2009-10-27 | System for monitoring ablation size |
US14/064,846 US8894641B2 (en) | 2009-10-27 | 2013-10-28 | System and method for monitoring ablation size |
US14/532,317 US10004559B2 (en) | 2009-10-27 | 2014-11-04 | System and method for monitoring ablation size |
US16/018,855 US20180296266A1 (en) | 2009-10-27 | 2018-06-26 | System and method for monitoring ablation size |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US14/532,317 Continuation US10004559B2 (en) | 2009-10-27 | 2014-11-04 | System and method for monitoring ablation size |
Publications (1)
Publication Number | Publication Date |
---|---|
US20180296266A1 true US20180296266A1 (en) | 2018-10-18 |
Family
ID=43513911
Family Applications (4)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US12/606,769 Active 2031-11-20 US8568401B2 (en) | 2009-10-27 | 2009-10-27 | System for monitoring ablation size |
US14/064,846 Active US8894641B2 (en) | 2009-10-27 | 2013-10-28 | System and method for monitoring ablation size |
US14/532,317 Active 2032-01-17 US10004559B2 (en) | 2009-10-27 | 2014-11-04 | System and method for monitoring ablation size |
US16/018,855 Abandoned US20180296266A1 (en) | 2009-10-27 | 2018-06-26 | System and method for monitoring ablation size |
Family Applications Before (3)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US12/606,769 Active 2031-11-20 US8568401B2 (en) | 2009-10-27 | 2009-10-27 | System for monitoring ablation size |
US14/064,846 Active US8894641B2 (en) | 2009-10-27 | 2013-10-28 | System and method for monitoring ablation size |
US14/532,317 Active 2032-01-17 US10004559B2 (en) | 2009-10-27 | 2014-11-04 | System and method for monitoring ablation size |
Country Status (3)
Country | Link |
---|---|
US (4) | US8568401B2 (en) |
EP (1) | EP2316371B1 (en) |
JP (4) | JP5580168B2 (en) |
Families Citing this family (72)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7653438B2 (en) | 2002-04-08 | 2010-01-26 | Ardian, Inc. | Methods and apparatus for renal neuromodulation |
US7553309B2 (en) | 2004-10-08 | 2009-06-30 | Covidien Ag | Electrosurgical system employing multiple electrodes and method thereof |
US20070021803A1 (en) | 2005-07-22 | 2007-01-25 | The Foundry Inc. | Systems and methods for neuromodulation for treatment of pain and other disorders associated with nerve conduction |
US9277969B2 (en) * | 2009-04-01 | 2016-03-08 | Covidien Lp | Microwave ablation system with user-controlled ablation size and method of use |
US8903488B2 (en) | 2009-05-28 | 2014-12-02 | Angiodynamics, Inc. | System and method for synchronizing energy delivery to the cardiac rhythm |
US8323275B2 (en) | 2009-06-19 | 2012-12-04 | Vivant Medical, Inc. | Laparoscopic port with microwave rectifier |
US9895189B2 (en) | 2009-06-19 | 2018-02-20 | Angiodynamics, Inc. | Methods of sterilization and treating infection using irreversible electroporation |
US8069553B2 (en) | 2009-09-09 | 2011-12-06 | Vivant Medical, Inc. | Method for constructing a dipole antenna |
US9113925B2 (en) * | 2009-09-09 | 2015-08-25 | Covidien Lp | System and method for performing an ablation procedure |
US9095359B2 (en) | 2009-09-18 | 2015-08-04 | Covidien Lp | Tissue ablation system with energy distribution |
US8568398B2 (en) | 2009-09-29 | 2013-10-29 | Covidien Lp | Flow rate monitor for fluid cooled microwave ablation probe |
US8568401B2 (en) | 2009-10-27 | 2013-10-29 | Covidien Lp | System for monitoring ablation size |
US8382750B2 (en) | 2009-10-28 | 2013-02-26 | Vivant Medical, Inc. | System and method for monitoring ablation size |
US8430871B2 (en) | 2009-10-28 | 2013-04-30 | Covidien Lp | System and method for monitoring ablation size |
US8394092B2 (en) * | 2009-11-17 | 2013-03-12 | Vivant Medical, Inc. | Electromagnetic energy delivery devices including an energy applicator array and electrosurgical systems including same |
US8764744B2 (en) | 2010-01-25 | 2014-07-01 | Covidien Lp | System for monitoring ablation size |
US8491579B2 (en) | 2010-02-05 | 2013-07-23 | Covidien Lp | Electrosurgical devices with choke shorted to biological tissue |
US8968288B2 (en) | 2010-02-19 | 2015-03-03 | Covidien Lp | Ablation devices with dual operating frequencies, systems including same, and methods of adjusting ablation volume using same |
US8617153B2 (en) | 2010-02-26 | 2013-12-31 | Covidien Lp | Tunable microwave ablation probe |
US8728067B2 (en) | 2010-03-08 | 2014-05-20 | Covidien Lp | Microwave antenna probe having a deployable ground plane |
US10039601B2 (en) | 2010-03-26 | 2018-08-07 | Covidien Lp | Ablation devices with adjustable radiating section lengths, electrosurgical systems including same, and methods of adjusting ablation fields using same |
US8409188B2 (en) | 2010-03-26 | 2013-04-02 | Covidien Lp | Ablation devices with adjustable radiating section lengths, electrosurgical systems including same, and methods of adjusting ablation fields using same |
US9192436B2 (en) | 2010-05-25 | 2015-11-24 | Covidien Lp | Flow rate verification monitor for fluid-cooled microwave ablation probe |
US8652127B2 (en) | 2010-05-26 | 2014-02-18 | Covidien Lp | System and method for chemically cooling an ablation antenna |
US9241762B2 (en) | 2010-06-03 | 2016-01-26 | Covidien Lp | Specific absorption rate measurement and energy-delivery device characterization using image analysis |
US8672933B2 (en) | 2010-06-30 | 2014-03-18 | Covidien Lp | Microwave antenna having a reactively-loaded loop configuration |
US10588684B2 (en) | 2010-07-19 | 2020-03-17 | Covidien Lp | Hydraulic conductivity monitoring to initiate tissue division |
WO2012051433A2 (en) | 2010-10-13 | 2012-04-19 | Angiodynamics, Inc. | System and method for electrically ablating tissue of a patient |
JP6046041B2 (en) | 2010-10-25 | 2016-12-14 | メドトロニック アーディアン ルクセンブルク ソシエテ ア レスポンサビリテ リミテ | Devices, systems, and methods for neuromodulation therapy evaluation and feedback |
US9055957B2 (en) | 2010-12-23 | 2015-06-16 | Covidien Lp | Microwave field-detecting needle assemblies, methods of manufacturing same, methods of adjusting an ablation field radiating into tissue using same, and systems including same |
US9770294B2 (en) | 2011-01-05 | 2017-09-26 | Covidien Lp | Energy-delivery devices with flexible fluid-cooled shaft, inflow/outflow junctions suitable for use with same, and systems including same |
US9028476B2 (en) | 2011-02-03 | 2015-05-12 | Covidien Lp | Dual antenna microwave resection and ablation device, system and method of use |
US8992413B2 (en) | 2011-05-31 | 2015-03-31 | Covidien Lp | Modified wet tip antenna design |
CN104066368B (en) | 2011-09-22 | 2017-02-22 | 乔治华盛顿大学 | Systems and methods for visualizing ablated tissue |
ES2727868T3 (en) | 2011-09-22 | 2019-10-21 | Univ George Washington | Systems for visualizing ablated tissue |
US9078665B2 (en) | 2011-09-28 | 2015-07-14 | Angiodynamics, Inc. | Multiple treatment zone ablation probe |
WO2013076588A2 (en) | 2011-11-07 | 2013-05-30 | Medtronic Ardian Luxembourg S.A.R.L. | Endovascular nerve monitoring devices and associated systems and methods |
US9480523B2 (en) | 2012-01-27 | 2016-11-01 | Covidien Lp | Systems and methods for phase predictive impedance loss model calibration and compensation |
US9037447B2 (en) | 2012-01-27 | 2015-05-19 | Covidien Lp | Systems and methods for phase predictive impedance loss model calibration and compensation |
CA2865242A1 (en) | 2012-03-08 | 2013-09-12 | Medtronic Ardian Luxembourg S.A.R.L. | Biomarker sampling in the context of neuromodulation devices and associated systems and methods |
US9888956B2 (en) | 2013-01-22 | 2018-02-13 | Angiodynamics, Inc. | Integrated pump and generator device and method of use |
US10543037B2 (en) | 2013-03-15 | 2020-01-28 | Medtronic Ardian Luxembourg S.A.R.L. | Controlled neuromodulation systems and methods of use |
JP6177576B2 (en) * | 2013-04-26 | 2017-08-09 | アルフレッサファーマ株式会社 | Microwave supply apparatus and microwave surgical apparatus provided with the same |
US9339332B2 (en) | 2013-08-30 | 2016-05-17 | Medtronic Ardian Luxembourg S.A.R.L. | Neuromodulation catheters with nerve monitoring features for transmitting digital neural signals and associated systems and methods |
US9326816B2 (en) | 2013-08-30 | 2016-05-03 | Medtronic Ardian Luxembourg S.A.R.L. | Neuromodulation systems having nerve monitoring assemblies and associated devices, systems, and methods |
EP3071095A4 (en) | 2013-11-20 | 2017-07-26 | The George Washington University | Systems and methods for hyperspectral analysis of cardiac tissue |
US9901386B2 (en) | 2014-01-13 | 2018-02-27 | Covidien Lp | Systems and methods for multifrequency cable compensation |
US10610292B2 (en) | 2014-04-25 | 2020-04-07 | Medtronic Ardian Luxembourg S.A.R.L. | Devices, systems, and methods for monitoring and/or controlling deployment of a neuromodulation element within a body lumen and related technology |
CN106572884B (en) | 2014-08-20 | 2020-06-12 | 柯惠有限合伙公司 | System and method for spherical ablation |
WO2016033543A1 (en) | 2014-08-28 | 2016-03-03 | Medtronic Ardian Luxembourg S.A.R.L. | Methods for assessing efficacy of renal neuromodulation and associated systems and devices |
EP4389044A3 (en) | 2014-10-01 | 2024-09-11 | Medtronic Ardian Luxembourg S.à.r.l. | Systems and methods for evaluating neuromodulation therapy via hemodynamic responses |
EP3215002B1 (en) | 2014-11-03 | 2024-03-20 | The George Washington University | Systems for lesion assessment |
KR102612185B1 (en) | 2014-11-03 | 2023-12-08 | 460메디컬, 인크. | Systems and methods for assessment of contact quality |
WO2016100720A1 (en) | 2014-12-17 | 2016-06-23 | Medtronic Ardian Luxembourg S.A.R.L. | Systems and methods for assessing sympathetic nervous system tone for renal neuromodulation therapy |
WO2016109437A1 (en) | 2014-12-31 | 2016-07-07 | Covidien Lp | System and method for treating copd and emphysema |
US10779904B2 (en) | 2015-07-19 | 2020-09-22 | 460Medical, Inc. | Systems and methods for lesion formation and assessment |
US10660691B2 (en) | 2015-10-07 | 2020-05-26 | Angiodynamics, Inc. | Multiple use subassembly with integrated fluid delivery system for use with single or dual-lumen peristaltic tubing |
US11324442B1 (en) | 2015-11-25 | 2022-05-10 | Maquet Cardiovascular Llc | Broadband impedance spectroscopy and its use for tissue welding |
CA2967728C (en) | 2016-05-19 | 2020-08-25 | Covidien Lp | Modular microwave generators and methods for operating modular microwave generators |
KR20190062419A (en) | 2016-10-04 | 2019-06-05 | 아벤트, 인크. | The cooled RF probe |
US10231784B2 (en) | 2016-10-28 | 2019-03-19 | Medtronic Ardian Luxembourg S.A.R.L. | Methods and systems for optimizing perivascular neuromodulation therapy using computational fluid dynamics |
US10905492B2 (en) | 2016-11-17 | 2021-02-02 | Angiodynamics, Inc. | Techniques for irreversible electroporation using a single-pole tine-style internal device communicating with an external surface electrode |
CN107374726B (en) * | 2017-08-31 | 2023-10-20 | 绵阳立德电子股份有限公司 | Radio frequency ablation electrode needle with adjustable working length and mounting method |
US12082917B2 (en) | 2018-01-24 | 2024-09-10 | Medtronic Ireland Manufacturing Unlimited Company | Systems, devices, and methods for assessing efficacy of renal neuromodulation therapy |
US11633120B2 (en) | 2018-09-04 | 2023-04-25 | Medtronic Ardian Luxembourg S.A.R.L. | Systems and methods for assessing efficacy of renal neuromodulation therapy |
CN210673430U (en) * | 2018-09-14 | 2020-06-05 | 杭州堃博生物科技有限公司 | Bendable radio frequency ablation catheter |
CN109771025B (en) * | 2019-01-03 | 2020-06-30 | 杭州电子科技大学 | Impedance detection module for medical equipment cloud system |
WO2021108704A1 (en) * | 2019-11-27 | 2021-06-03 | Blossom Innovations, LLC | Devices, systems and methods for tissue analysis, location determination and tissue ablation |
EP4087511A4 (en) | 2020-01-08 | 2024-02-14 | 460Medical, Inc. | Systems and methods for optical interrogation of ablation lesions |
EP4209189A4 (en) * | 2020-09-03 | 2024-03-06 | Hangzhou Nuo Cheng Medical Instrument Co., Ltd | Living body impedance detection device and radio frequency ablation system |
CN117717408A (en) * | 2022-11-03 | 2024-03-19 | 上海微创电生理医疗科技股份有限公司 | Readable storage medium, ablation system, and electronic device |
CN117637173B (en) * | 2023-11-29 | 2024-07-19 | 南京诺源医疗器械有限公司 | Method and device for determining microwave ablation parameters and electronic equipment |
Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20020077627A1 (en) * | 2000-07-25 | 2002-06-20 | Johnson Theodore C. | Method for detecting and treating tumors using localized impedance measurement |
US20040215183A1 (en) * | 1995-02-22 | 2004-10-28 | Medtronic, Inc. | Apparatus and method for creating, maintaining, and controlling a virtual electrode used for the ablation of tissue |
Family Cites Families (279)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
FR379607A (en) | 1907-06-15 | 1907-11-13 | Samuel Bruce | Safety device for elevator |
DE390937C (en) | 1922-10-13 | 1924-03-03 | Adolf Erb | Device for internal heating of furnace furnaces for hardening, tempering, annealing, quenching and melting |
US1595154A (en) | 1924-11-06 | 1926-08-10 | Aubrey R Harrison | Automatic railway-crossing gate |
DE1099658B (en) | 1959-04-29 | 1961-02-16 | Siemens Reiniger Werke Ag | Automatic switch-on device for high-frequency surgical devices |
FR1275415A (en) | 1960-09-26 | 1961-11-10 | Device for detecting disturbances for electrical installations, in particular electrosurgery | |
DE1139927B (en) | 1961-01-03 | 1962-11-22 | Friedrich Laber | High-frequency surgical device |
DE1149832C2 (en) | 1961-02-25 | 1977-10-13 | Siemens AG, 1000 Berlin und 8000 München | HIGH FREQUENCY SURGICAL EQUIPMENT |
FR1347865A (en) | 1962-11-22 | 1964-01-04 | Improvements to diathermo-coagulation devices | |
DE1439302B2 (en) | 1963-10-26 | 1971-05-19 | Siemens AG, 1000 Berlin u 8000 München | High frequency surgical device |
US3631363A (en) | 1969-11-14 | 1971-12-28 | Gen Electric | High-frequency cavity oscillator having improved tuning means |
SU401367A1 (en) | 1971-10-05 | 1973-10-12 | Тернопольский государственный медицинский институт | BIAKTIVNYE ELECTRO SURGICAL INSTRUMENT |
FR2235669A1 (en) | 1973-07-07 | 1975-01-31 | Lunacek Boris | Gynaecological sterilisation instrument - has hollow electrode protruding from the end of a curved ended tube |
GB1480736A (en) | 1973-08-23 | 1977-07-20 | Matburn Ltd | Electrodiathermy apparatus |
FR2251864A1 (en) | 1973-11-21 | 1975-06-13 | Termiflex Corp | Portable input and output unit for connection to a data processor - is basically a calculator with transmitter and receiver |
DE2407559C3 (en) | 1974-02-16 | 1982-01-21 | Dornier System Gmbh, 7990 Friedrichshafen | Heat probe |
DE2415263A1 (en) | 1974-03-29 | 1975-10-02 | Aesculap Werke Ag | Surgical H.F. coagulation probe has electrode tongs - with exposed ends of insulated conductors forming tong-jaws |
DE2429021C2 (en) | 1974-06-18 | 1983-12-08 | Erbe Elektromedizin GmbH, 7400 Tübingen | Remote switching device for an HF surgical device |
FR2276027A1 (en) | 1974-06-25 | 1976-01-23 | Medical Plastics Inc | Plate electrode with connector - is clamped between connector jaws held by releasable locking device |
DE2460481A1 (en) | 1974-12-20 | 1976-06-24 | Delma Elektro Med App | Electrode grip for remote HF surgical instrument switching - has shaped insulated piece with contact ring of sterilizable (silicon) rubber |
US4237887A (en) | 1975-01-23 | 1980-12-09 | Valleylab, Inc. | Electrosurgical device |
DE2504280C3 (en) | 1975-02-01 | 1980-08-28 | Hans Heinrich Prof. Dr. 8035 Gauting Meinke | Device for cutting and / or coagulating human tissue with high frequency current |
CA1064581A (en) | 1975-06-02 | 1979-10-16 | Stephen W. Andrews | Pulse control circuit and method for electrosurgical units |
FR2315286A2 (en) | 1975-06-26 | 1977-01-21 | Lamidey Marcel | H.F. blood coagulating dissecting forceps - with adjustable stops to vary clamping space and circuit making contacts |
DE2540968C2 (en) | 1975-09-13 | 1982-12-30 | Erbe Elektromedizin GmbH, 7400 Tübingen | Device for switching on the coagulation current of a bipolar coagulation forceps |
FR2390968A1 (en) | 1977-05-16 | 1978-12-15 | Skovajsa Joseph | Local acupuncture treatment appts. - has oblong head with end aperture and contains laser diode unit (NL 20.11.78) |
SU727201A2 (en) | 1977-11-02 | 1980-04-15 | Киевский Научно-Исследовательский Институт Нейрохирургии | Electric surgical apparatus |
DE2803275C3 (en) | 1978-01-26 | 1980-09-25 | Aesculap-Werke Ag Vormals Jetter & Scheerer, 7200 Tuttlingen | Remote switching device for switching a monopolar HF surgical device |
DE2823291A1 (en) | 1978-05-27 | 1979-11-29 | Rainer Ing Grad Koch | Coagulation instrument automatic HF switching circuit - has first lead to potentiometer and second to transistor base |
DE2946728A1 (en) | 1979-11-20 | 1981-05-27 | Erbe Elektromedizin GmbH & Co KG, 7400 Tübingen | HF surgical appts. for use with endoscope - provides cutting or coagulation current at preset intervals and of selected duration |
USD263020S (en) | 1980-01-22 | 1982-02-16 | Rau Iii David M | Retractable knife |
US4798215A (en) | 1984-03-15 | 1989-01-17 | Bsd Medical Corporation | Hyperthermia apparatus |
US4462412A (en) | 1980-04-02 | 1984-07-31 | Bsd Medical Corporation | Annular electromagnetic radiation applicator for biological tissue, and method |
US5097844A (en) | 1980-04-02 | 1992-03-24 | Bsd Medical Corporation | Hyperthermia apparatus having three-dimensional focusing |
USD266842S (en) | 1980-06-27 | 1982-11-09 | Villers Mark W | Phonograph record spacer |
USD278306S (en) | 1980-06-30 | 1985-04-09 | Mcintosh Lois A | Microwave oven rack |
JPS5778844A (en) | 1980-11-04 | 1982-05-17 | Kogyo Gijutsuin | Lasre knife |
DE3045996A1 (en) | 1980-12-05 | 1982-07-08 | Medic Eschmann Handelsgesellschaft für medizinische Instrumente mbH, 2000 Hamburg | Electro-surgical scalpel instrument - has power supply remotely controlled by surgeon |
FR2502935B1 (en) | 1981-03-31 | 1985-10-04 | Dolley Roger | METHOD AND DEVICE FOR CONTROLLING THE COAGULATION OF TISSUES USING A HIGH FREQUENCY CURRENT |
DE3120102A1 (en) | 1981-05-20 | 1982-12-09 | F.L. Fischer GmbH & Co, 7800 Freiburg | ARRANGEMENT FOR HIGH-FREQUENCY COAGULATION OF EGG WHITE FOR SURGICAL PURPOSES |
US4397313A (en) | 1981-08-03 | 1983-08-09 | Clini-Therm Corporation | Multiple microwave applicator system and method for microwave hyperthermia treatment |
FR2517953A1 (en) | 1981-12-10 | 1983-06-17 | Alvar Electronic | Diaphanometer for optical examination of breast tissue structure - measures tissue transparency using two plates and optical fibre bundle cooperating with photoelectric cells |
FR2546409B1 (en) | 1983-05-26 | 1988-05-13 | Cgr Mev | HYPERTHERMIA APPARATUS |
FR2573301B3 (en) | 1984-11-16 | 1987-04-30 | Lamidey Gilles | SURGICAL PLIERS AND ITS CONTROL AND CONTROL APPARATUS |
DE3510586A1 (en) | 1985-03-23 | 1986-10-02 | Erbe Elektromedizin GmbH, 7400 Tübingen | Control device for a high-frequency surgical instrument |
USD295893S (en) | 1985-09-25 | 1988-05-24 | Acme United Corporation | Disposable surgical clamp |
USD295894S (en) | 1985-09-26 | 1988-05-24 | Acme United Corporation | Disposable surgical scissors |
DE3604823C2 (en) | 1986-02-15 | 1995-06-01 | Lindenmeier Heinz | High frequency generator with automatic power control for high frequency surgery |
JPH055106Y2 (en) | 1986-02-28 | 1993-02-09 | ||
EP0246350A1 (en) | 1986-05-23 | 1987-11-25 | Erbe Elektromedizin GmbH. | Coagulation electrode |
JPS62284659A (en) | 1986-05-31 | 1987-12-10 | 株式会社島津製作所 | Ultrasonic hyperthermia apparatus |
JPH0540112Y2 (en) | 1987-03-03 | 1993-10-12 | ||
DE3711511C1 (en) | 1987-04-04 | 1988-06-30 | Hartmann & Braun Ag | Method for determining gas concentrations in a gas mixture and sensor for measuring thermal conductivity |
DE8712328U1 (en) | 1987-09-11 | 1988-02-18 | Jakoubek, Franz, 7201 Emmingen-Liptingen | Endoscopy forceps |
DE3824970C2 (en) * | 1988-07-22 | 1999-04-01 | Lindenmeier Heinz | Feedback high frequency power oscillator |
DE3904558C2 (en) | 1989-02-15 | 1997-09-18 | Lindenmeier Heinz | Automatically power-controlled high-frequency generator for high-frequency surgery |
DE3942998C2 (en) | 1989-12-27 | 1998-11-26 | Delma Elektro Med App | High frequency electrosurgical unit |
JP2806511B2 (en) | 1990-07-31 | 1998-09-30 | 松下電工株式会社 | Manufacturing method of sintered alloy |
JP2951418B2 (en) | 1991-02-08 | 1999-09-20 | トキコ株式会社 | Sample liquid component analyzer |
US5417210A (en) | 1992-05-27 | 1995-05-23 | International Business Machines Corporation | System and method for augmentation of endoscopic surgery |
DE4122050C2 (en) | 1991-07-03 | 1996-05-30 | Gore W L & Ass Gmbh | Antenna arrangement with supply line for medical heat application in body cavities |
US5383874A (en) * | 1991-11-08 | 1995-01-24 | Ep Technologies, Inc. | Systems for identifying catheters and monitoring their use |
DE4238263A1 (en) | 1991-11-15 | 1993-05-19 | Minnesota Mining & Mfg | Adhesive comprising hydrogel and crosslinked polyvinyl:lactam - is used in electrodes for biomedical application providing low impedance and good mechanical properties when water and/or moisture is absorbed from skin |
DE4205213A1 (en) | 1992-02-20 | 1993-08-26 | Delma Elektro Med App | HIGH FREQUENCY SURGERY DEVICE |
FR2687786B1 (en) | 1992-02-26 | 1994-05-06 | Pechiney Recherche | MEASUREMENT OF ELECTRICAL RESISTIVITY AND HIGH TEMPERATURE THERMAL CONDUCTIVITY OF REFRACTORY PRODUCTS. |
USD354218S (en) | 1992-10-01 | 1995-01-10 | Fiberslab Pty Limited | Spacer for use in concrete construction |
DE4303882C2 (en) | 1993-02-10 | 1995-02-09 | Kernforschungsz Karlsruhe | Combination instrument for separation and coagulation for minimally invasive surgery |
GB9309142D0 (en) | 1993-05-04 | 1993-06-16 | Gyrus Medical Ltd | Laparoscopic instrument |
ZA948393B (en) * | 1993-11-01 | 1995-06-26 | Polartechnics Ltd | Method and apparatus for tissue type recognition |
GB9322464D0 (en) | 1993-11-01 | 1993-12-22 | Gyrus Medical Ltd | Electrosurgical apparatus |
US5472441A (en) | 1993-11-08 | 1995-12-05 | Zomed International | Device for treating cancer and non-malignant tumors and methods |
DE4339049C2 (en) | 1993-11-16 | 2001-06-28 | Erbe Elektromedizin | Surgical system configuration facility |
US6464689B1 (en) | 1999-09-08 | 2002-10-15 | Curon Medical, Inc. | Graphical user interface for monitoring and controlling use of medical devices |
GB9413070D0 (en) | 1994-06-29 | 1994-08-17 | Gyrus Medical Ltd | Electrosurgical apparatus |
GB9425781D0 (en) | 1994-12-21 | 1995-02-22 | Gyrus Medical Ltd | Electrosurgical instrument |
US6106524A (en) * | 1995-03-03 | 2000-08-22 | Neothermia Corporation | Methods and apparatus for therapeutic cauterization of predetermined volumes of biological tissue |
US6246898B1 (en) | 1995-03-28 | 2001-06-12 | Sonometrics Corporation | Method for carrying out a medical procedure using a three-dimensional tracking and imaging system |
DE69635423T2 (en) | 1995-05-04 | 2006-06-08 | Sherwood Services Ag | THERMAL SURGERY SYSTEM WITH COLD ELECTRIC TIP |
US6575969B1 (en) * | 1995-05-04 | 2003-06-10 | Sherwood Services Ag | Cool-tip radiofrequency thermosurgery electrode system for tumor ablation |
US6293942B1 (en) | 1995-06-23 | 2001-09-25 | Gyrus Medical Limited | Electrosurgical generator method |
US5800484A (en) | 1995-08-15 | 1998-09-01 | Rita Medical Systems, Inc. | Multiple antenna ablation apparatus with expanded electrodes |
US6235023B1 (en) | 1995-08-15 | 2001-05-22 | Rita Medical Systems, Inc. | Cell necrosis apparatus |
US5863290A (en) | 1995-08-15 | 1999-01-26 | Rita Medical Systems | Multiple antenna ablation apparatus and method |
US6132425A (en) * | 1995-08-15 | 2000-10-17 | Gough; Edward J. | Cell necrosis apparatus |
US6059780A (en) * | 1995-08-15 | 2000-05-09 | Rita Medical Systems, Inc. | Multiple antenna ablation apparatus and method with cooling element |
US6073051A (en) | 1996-08-13 | 2000-06-06 | Oratec Interventions, Inc. | Apparatus for treating intervertebal discs with electromagnetic energy |
JP3782495B2 (en) * | 1995-10-27 | 2006-06-07 | アルフレッサファーマ株式会社 | Microwave surgical device |
US6350276B1 (en) | 1996-01-05 | 2002-02-26 | Thermage, Inc. | Tissue remodeling apparatus containing cooling fluid |
DE19608716C1 (en) | 1996-03-06 | 1997-04-17 | Aesculap Ag | Bipolar surgical holding instrument |
US6016452A (en) * | 1996-03-19 | 2000-01-18 | Kasevich; Raymond S. | Dynamic heating method and radio frequency thermal treatment |
US5836942A (en) | 1996-04-04 | 1998-11-17 | Minnesota Mining And Manufacturing Company | Biomedical electrode with lossy dielectric properties |
US5904709A (en) | 1996-04-17 | 1999-05-18 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Microwave treatment for cardiac arrhythmias |
US5797902A (en) * | 1996-05-10 | 1998-08-25 | Minnesota Mining And Manufacturing Company | Biomedical electrode providing early detection of accidental detachment |
US6126682A (en) | 1996-08-13 | 2000-10-03 | Oratec Interventions, Inc. | Method for treating annular fissures in intervertebral discs |
US5836943A (en) * | 1996-08-23 | 1998-11-17 | Team Medical, L.L.C. | Electrosurgical generator |
DE29616210U1 (en) | 1996-09-18 | 1996-11-14 | Olympus Winter & Ibe Gmbh, 22045 Hamburg | Handle for surgical instruments |
DE19643127A1 (en) | 1996-10-18 | 1998-04-23 | Berchtold Gmbh & Co Geb | High frequency surgical device and method for its operation |
US5923475A (en) | 1996-11-27 | 1999-07-13 | Eastman Kodak Company | Laser printer using a fly's eye integrator |
JPH10243947A (en) * | 1997-03-04 | 1998-09-14 | Olympus Optical Co Ltd | High-frequency device |
WO1998044856A1 (en) * | 1997-04-04 | 1998-10-15 | Minnesota Mining And Manufacturing Company | Method and apparatus for controlling contact of biomedical electrodes with patient skin |
DE19717411A1 (en) | 1997-04-25 | 1998-11-05 | Aesculap Ag & Co Kg | Monitoring of thermal loading of patient tissue in contact region of neutral electrode of HF treatment unit |
ES2371067T3 (en) * | 1997-07-25 | 2011-12-27 | Covidien Ag | ABLATION ELECTRODE SYSTEM IN RACE. |
US6007532A (en) | 1997-08-29 | 1999-12-28 | 3M Innovative Properties Company | Method and apparatus for detecting loss of contact of biomedical electrodes with patient skin |
DE19739699A1 (en) | 1997-09-04 | 1999-03-11 | Laser & Med Tech Gmbh | Electrode arrangement for the electro-thermal treatment of the human or animal body |
DE19751108A1 (en) | 1997-11-18 | 1999-05-20 | Beger Frank Michael Dipl Desig | Electrosurgical operation tool, especially for diathermy |
US6031375A (en) | 1997-11-26 | 2000-02-29 | The Johns Hopkins University | Method of magnetic resonance analysis employing cylindrical coordinates and an associated apparatus |
EP0923907A1 (en) | 1997-12-19 | 1999-06-23 | Gyrus Medical Limited | An electrosurgical instrument |
DE19801173C1 (en) | 1998-01-15 | 1999-07-15 | Kendall Med Erzeugnisse Gmbh | Clamp connector for film electrodes |
US6273886B1 (en) | 1998-02-19 | 2001-08-14 | Curon Medical, Inc. | Integrated tissue heating and cooling apparatus |
US6358245B1 (en) | 1998-02-19 | 2002-03-19 | Curon Medical, Inc. | Graphical user interface for association with an electrode structure deployed in contact with a tissue region |
US6123702A (en) | 1998-09-10 | 2000-09-26 | Scimed Life Systems, Inc. | Systems and methods for controlling power in an electrosurgical probe |
US6245065B1 (en) | 1998-09-10 | 2001-06-12 | Scimed Life Systems, Inc. | Systems and methods for controlling power in an electrosurgical probe |
DE19848540A1 (en) | 1998-10-21 | 2000-05-25 | Reinhard Kalfhaus | Circuit layout and method for operating a single- or multiphase current inverter connects an AC voltage output to a primary winding and current and a working resistance to a transformer's secondary winding and current. |
USD425201S (en) | 1998-10-23 | 2000-05-16 | Sherwood Services Ag | Disposable electrode assembly |
USD449886S1 (en) | 1998-10-23 | 2001-10-30 | Sherwood Services Ag | Forceps with disposable electrode |
USD424694S (en) | 1998-10-23 | 2000-05-09 | Sherwood Services Ag | Forceps |
US6701176B1 (en) | 1998-11-04 | 2004-03-02 | Johns Hopkins University School Of Medicine | Magnetic-resonance-guided imaging, electrophysiology, and ablation |
US6451015B1 (en) | 1998-11-18 | 2002-09-17 | Sherwood Services Ag | Method and system for menu-driven two-dimensional display lesion generator |
US20020022836A1 (en) | 1999-03-05 | 2002-02-21 | Gyrus Medical Limited | Electrosurgery system |
US6375606B1 (en) | 1999-03-17 | 2002-04-23 | Stereotaxis, Inc. | Methods of and apparatus for treating vascular defects |
USD424693S (en) | 1999-04-08 | 2000-05-09 | Pruter Rick L | Needle guide for attachment to an ultrasound transducer probe |
US6308089B1 (en) * | 1999-04-14 | 2001-10-23 | O.B. Scientific, Inc. | Limited use medical probe |
GB9911954D0 (en) | 1999-05-21 | 1999-07-21 | Gyrus Medical Ltd | Electrosurgery system and instrument |
GB9911956D0 (en) | 1999-05-21 | 1999-07-21 | Gyrus Medical Ltd | Electrosurgery system and method |
GB9912627D0 (en) | 1999-05-28 | 1999-07-28 | Gyrus Medical Ltd | An electrosurgical instrument |
GB9912625D0 (en) | 1999-05-28 | 1999-07-28 | Gyrus Medical Ltd | An electrosurgical generator and system |
GB9913652D0 (en) | 1999-06-11 | 1999-08-11 | Gyrus Medical Ltd | An electrosurgical generator |
US6692489B1 (en) * | 1999-07-21 | 2004-02-17 | Team Medical, Llc | Electrosurgical mode conversion system |
JP2001037775A (en) * | 1999-07-26 | 2001-02-13 | Olympus Optical Co Ltd | Treatment device |
JP2003508150A (en) * | 1999-09-08 | 2003-03-04 | キューロン メディカル,インコーポレイテッド | Systems and methods for monitoring and controlling use of medical devices |
CA2384025A1 (en) | 1999-09-08 | 2001-03-15 | Curon Medical, Inc. | System for controlling a family of treatment devices |
EP1218801A4 (en) * | 1999-09-08 | 2009-07-01 | Mederi Therapeutics Inc | Systems and methods for monitoring and controlling use of medical devices |
US6725080B2 (en) | 2000-03-01 | 2004-04-20 | Surgical Navigation Technologies, Inc. | Multiple cannula image guided tool for image guided procedures |
US6869430B2 (en) | 2000-03-31 | 2005-03-22 | Rita Medical Systems, Inc. | Tissue biopsy and treatment apparatus and method |
DE10027727C1 (en) | 2000-06-03 | 2001-12-06 | Aesculap Ag & Co Kg | Scissors-shaped or forceps-shaped surgical instrument |
US6603994B2 (en) | 2000-12-28 | 2003-08-05 | Scimed Life Systems, Inc. | Apparatus and method for internally inducing a magnetic field in an aneurysm to embolize aneurysm with magnetically-controllable substance |
AU2002245243B2 (en) | 2001-01-11 | 2007-03-22 | Angiodynamics, Inc. | Bone-treatment instrument and method |
US20080125775A1 (en) * | 2001-02-28 | 2008-05-29 | Morris David L | Hemostasis and/or coagulation of tissue |
USD457959S1 (en) | 2001-04-06 | 2002-05-28 | Sherwood Services Ag | Vessel sealer |
USD457958S1 (en) | 2001-04-06 | 2002-05-28 | Sherwood Services Ag | Vessel sealer and divider |
WO2002089686A1 (en) | 2001-05-10 | 2002-11-14 | Rita Medical Systems, Inc. | Rf tissue ablation apparatus and method |
ATE320767T1 (en) * | 2001-09-28 | 2006-04-15 | Rita Medical Systems Inc | IMPEDANCE CONTROLLED DEVICE FOR TISSUE ABLATION |
US6878147B2 (en) * | 2001-11-02 | 2005-04-12 | Vivant Medical, Inc. | High-strength microwave antenna assemblies |
DE10224154A1 (en) | 2002-05-27 | 2003-12-18 | Celon Ag Medical Instruments | Application device for electrosurgical device for body tissue removal via of HF current has electrode subset selected from active electrode set in dependence on measured impedance of body tissue |
US7439736B2 (en) | 2002-09-27 | 2008-10-21 | The Trustees Of Dartmouth College | Imaging by magnetic resonance adsorption, elastography and tomography |
US7041096B2 (en) * | 2002-10-24 | 2006-05-09 | Synergetics Usa, Inc. | Electrosurgical generator apparatus |
US7697972B2 (en) | 2002-11-19 | 2010-04-13 | Medtronic Navigation, Inc. | Navigation system for cardiac therapies |
USD487039S1 (en) | 2002-11-27 | 2004-02-24 | Robert Bosch Corporation | Spacer |
JP2004290266A (en) | 2003-03-25 | 2004-10-21 | Olympus Corp | Treating apparatus |
AU2003901390A0 (en) | 2003-03-26 | 2003-04-10 | University Of Technology, Sydney | Microwave antenna for cardiac ablation |
US20070276361A1 (en) * | 2003-03-28 | 2007-11-29 | Debbie Stevens-Wright | Method and apparatus for adjusting electrode dimensions |
USD499181S1 (en) | 2003-05-15 | 2004-11-30 | Sherwood Services Ag | Handle for a vessel sealer and divider |
USD496997S1 (en) | 2003-05-15 | 2004-10-05 | Sherwood Services Ag | Vessel sealer and divider |
DE10328514B3 (en) | 2003-06-20 | 2005-03-03 | Aesculap Ag & Co. Kg | Endoscopic surgical scissor instrument has internal pushrod terminating at distal end in transverse cylindrical head |
US7311703B2 (en) * | 2003-07-18 | 2007-12-25 | Vivant Medical, Inc. | Devices and methods for cooling microwave antennas |
AU2004279676B2 (en) | 2003-10-03 | 2011-10-13 | Uk Investment Associates Llc | Device and method for the treatment of hollow anatomical structures |
US7282050B2 (en) | 2003-10-31 | 2007-10-16 | Medtronic, Inc. | Ablation of exterior of stomach to treat obesity |
FR2862813B1 (en) | 2003-11-20 | 2006-06-02 | Pellenc Sa | METHOD FOR BALANCED LOADING OF LITHIUM-ION OR POLYMER LITHIUM BATTERY |
FR2864439B1 (en) | 2003-12-30 | 2010-12-03 | Image Guided Therapy | DEVICE FOR TREATING A VOLUME OF BIOLOGICAL TISSUE BY LOCALIZED HYPERTHERMIA |
JP2005268312A (en) | 2004-03-16 | 2005-09-29 | Semiconductor Leading Edge Technologies Inc | Resist removing method and semiconductor device manufactured using same |
US20050228251A1 (en) | 2004-03-30 | 2005-10-13 | General Electric Company | System and method for displaying a three-dimensional image of an organ or structure inside the body |
USD541938S1 (en) | 2004-04-09 | 2007-05-01 | Sherwood Services Ag | Open vessel sealer with mechanical cutter |
US7467015B2 (en) | 2004-04-29 | 2008-12-16 | Neuwave Medical, Inc. | Segmented catheter for tissue ablation |
DE102004022206B4 (en) | 2004-05-04 | 2006-05-11 | Bundesrepublik Deutschland, vertr. d. d. Bundesministerium für Wirtschaft und Arbeit, dieses vertr. d. d. Präsidenten der Physikalisch-Technischen Bundesanstalt | Sensor for measuring thermal conductivity comprises a strip composed of two parallel sections, and two outer heating strips |
DE602005024952D1 (en) | 2004-05-26 | 2011-01-05 | Medical Device Innovations Ltd | TISSUE DETECTION AND ABLATION DEVICE |
USD533942S1 (en) | 2004-06-30 | 2006-12-19 | Sherwood Services Ag | Open vessel sealer with mechanical cutter |
US20080015664A1 (en) | 2004-10-06 | 2008-01-17 | Podhajsky Ronald J | Systems and methods for thermally profiling radiofrequency electrodes |
USD535027S1 (en) | 2004-10-06 | 2007-01-09 | Sherwood Services Ag | Low profile vessel sealing and cutting mechanism |
USD525361S1 (en) | 2004-10-06 | 2006-07-18 | Sherwood Services Ag | Hemostat style elongated dissecting and dividing instrument |
USD531311S1 (en) | 2004-10-06 | 2006-10-31 | Sherwood Services Ag | Pistol grip style elongated dissecting and dividing instrument |
USD541418S1 (en) | 2004-10-06 | 2007-04-24 | Sherwood Services Ag | Lung sealing device |
USD564662S1 (en) | 2004-10-13 | 2008-03-18 | Sherwood Services Ag | Hourglass-shaped knife for electrosurgical forceps |
US8617152B2 (en) | 2004-11-15 | 2013-12-31 | Medtronic Ablation Frontiers Llc | Ablation system with feedback |
USD576932S1 (en) | 2005-03-01 | 2008-09-16 | Robert Bosch Gmbh | Spacer |
US9474564B2 (en) * | 2005-03-31 | 2016-10-25 | Covidien Ag | Method and system for compensating for external impedance of an energy carrying component when controlling an electrosurgical generator |
CN102225023B (en) | 2005-07-21 | 2014-04-02 | 泰科医疗集团有限合伙公司 | Systems and methods for treating a hollow anatomical structure |
US20070066971A1 (en) | 2005-09-21 | 2007-03-22 | Podhajsky Ronald J | Method and system for treating pain during an electrosurgical procedure |
DE202005015147U1 (en) | 2005-09-26 | 2006-02-09 | Health & Life Co., Ltd., Chung-Ho | Biosensor test strip with identifying function for biological measuring instruments has functioning electrode and counter electrode, identification zones with coating of electrically conductive material and reaction zone |
US7565207B2 (en) | 2005-11-22 | 2009-07-21 | Bsd Medical Corporation | Apparatus for creating hyperthermia in tissue |
US8685016B2 (en) * | 2006-01-24 | 2014-04-01 | Covidien Ag | System and method for tissue sealing |
US20070282320A1 (en) * | 2006-05-30 | 2007-12-06 | Sherwood Services Ag | System and method for controlling tissue heating rate prior to cellular vaporization |
ATE494040T1 (en) * | 2006-06-28 | 2011-01-15 | Ardian Inc | SYSTEMS FOR HEAT-INDUCED RENAL NEUROMODULATION |
JP5258772B2 (en) * | 2006-10-10 | 2013-08-07 | メディカル・デバイス・イノベーションズ・リミテッド | Apparatus and antenna calibration system and method for processing tissue using microwave radiation |
US8267927B2 (en) * | 2007-01-24 | 2012-09-18 | Koninklijke Philips Electronics N.V. | Advanced ablation planning |
US8211099B2 (en) | 2007-01-31 | 2012-07-03 | Tyco Healthcare Group Lp | Thermal feedback systems and methods of using the same |
DE102007009652A1 (en) | 2007-02-26 | 2008-09-04 | Körber Ag | Dummy device for patient-based medication using medicinal or pharmaceutical or dietary supplement products for patient, is true-to-original visual reproduction of real packaging section having actual products |
US7885625B2 (en) * | 2007-03-13 | 2011-02-08 | Texas Instruments Incorporated | RF A/D converter with phased feedback to low noise amplifier |
US9023024B2 (en) * | 2007-06-20 | 2015-05-05 | Covidien Lp | Reflective power monitoring for microwave applications |
GB0718721D0 (en) * | 2007-09-25 | 2007-11-07 | Medical Device Innovations Ltd | Surgical resection apparatus |
US7713076B2 (en) * | 2007-11-27 | 2010-05-11 | Vivant Medical, Inc. | Floating connector for microwave surgical device |
US8292880B2 (en) | 2007-11-27 | 2012-10-23 | Vivant Medical, Inc. | Targeted cooling of deployable microwave antenna |
DE102008061418A1 (en) * | 2007-12-12 | 2009-06-18 | Erbe Elektromedizin Gmbh | Apparatus for contactless communication and use of a memory device |
US7642451B2 (en) | 2008-01-23 | 2010-01-05 | Vivant Medical, Inc. | Thermally tuned coaxial cable for microwave antennas |
US8945111B2 (en) | 2008-01-23 | 2015-02-03 | Covidien Lp | Choked dielectric loaded tip dipole microwave antenna |
US8435237B2 (en) | 2008-01-29 | 2013-05-07 | Covidien Lp | Polyp encapsulation system and method |
US8353902B2 (en) | 2008-01-31 | 2013-01-15 | Vivant Medical, Inc. | Articulating ablation device and method |
US8262703B2 (en) | 2008-01-31 | 2012-09-11 | Vivant Medical, Inc. | Medical device including member that deploys in a spiral-like configuration and method |
US8221418B2 (en) * | 2008-02-07 | 2012-07-17 | Tyco Healthcare Group Lp | Endoscopic instrument for tissue identification |
US8965536B2 (en) | 2008-03-03 | 2015-02-24 | Covidien Lp | Intracooled percutaneous microwave ablation probe |
US9949794B2 (en) | 2008-03-27 | 2018-04-24 | Covidien Lp | Microwave ablation devices including expandable antennas and methods of use |
US9198723B2 (en) | 2008-03-31 | 2015-12-01 | Covidien Lp | Re-hydration antenna for ablation |
US8246614B2 (en) | 2008-04-17 | 2012-08-21 | Vivant Medical, Inc. | High-strength microwave antenna coupling |
US8059059B2 (en) * | 2008-05-29 | 2011-11-15 | Vivant Medical, Inc. | Slidable choke microwave antenna |
US9271796B2 (en) * | 2008-06-09 | 2016-03-01 | Covidien Lp | Ablation needle guide |
US8192427B2 (en) * | 2008-06-09 | 2012-06-05 | Tyco Healthcare Group Lp | Surface ablation process with electrode cooling methods |
US8343149B2 (en) * | 2008-06-26 | 2013-01-01 | Vivant Medical, Inc. | Deployable microwave antenna for treating tissue |
USD606203S1 (en) | 2008-07-04 | 2009-12-15 | Cambridge Temperature Concepts, Ltd. | Hand-held device |
US8608739B2 (en) | 2008-07-22 | 2013-12-17 | Covidien Lp | Electrosurgical devices, systems and methods of using the same |
US20100030206A1 (en) * | 2008-07-29 | 2010-02-04 | Brannan Joseph D | Tissue Ablation System With Phase-Controlled Channels |
US8834409B2 (en) * | 2008-07-29 | 2014-09-16 | Covidien Lp | Method for ablation volume determination and geometric reconstruction |
US9700366B2 (en) * | 2008-08-01 | 2017-07-11 | Covidien Lp | Polyphase electrosurgical system and method |
USD594736S1 (en) | 2008-08-13 | 2009-06-23 | Saint-Gobain Ceramics & Plastics, Inc. | Spacer support |
US8182480B2 (en) * | 2008-08-19 | 2012-05-22 | Tyco Healthcare Group Lp | Insulated tube for suction coagulator |
US20100045559A1 (en) * | 2008-08-25 | 2010-02-25 | Vivant Medical, Inc. | Dual-Band Dipole Microwave Ablation Antenna |
US9173706B2 (en) * | 2008-08-25 | 2015-11-03 | Covidien Lp | Dual-band dipole microwave ablation antenna |
US8211098B2 (en) * | 2008-08-25 | 2012-07-03 | Vivant Medical, Inc. | Microwave antenna assembly having a dielectric body portion with radial partitions of dielectric material |
US8251987B2 (en) * | 2008-08-28 | 2012-08-28 | Vivant Medical, Inc. | Microwave antenna |
US8394086B2 (en) * | 2008-09-03 | 2013-03-12 | Vivant Medical, Inc. | Microwave shielding apparatus |
US20100076422A1 (en) * | 2008-09-24 | 2010-03-25 | Tyco Healthcare Group Lp | Thermal Treatment of Nucleus Pulposus |
US8346370B2 (en) * | 2008-09-30 | 2013-01-01 | Vivant Medical, Inc. | Delivered energy generator for microwave ablation |
US20100087808A1 (en) * | 2008-10-03 | 2010-04-08 | Vivant Medical, Inc. | Combined Frequency Microwave Ablation System, Devices and Methods of Use |
US8512328B2 (en) * | 2008-10-13 | 2013-08-20 | Covidien Lp | Antenna assemblies for medical applications |
US9375272B2 (en) * | 2008-10-13 | 2016-06-28 | Covidien Lp | Antenna assemblies for medical applications |
US9113624B2 (en) * | 2008-10-15 | 2015-08-25 | Covidien Lp | System and method for perfusing biological organs |
US9113924B2 (en) * | 2008-10-17 | 2015-08-25 | Covidien Lp | Choked dielectric loaded tip dipole microwave antenna |
USD594737S1 (en) | 2008-10-28 | 2009-06-23 | Mmi Management Services Lp | Rebar chair |
US8262652B2 (en) * | 2009-01-12 | 2012-09-11 | Tyco Healthcare Group Lp | Imaginary impedance process monitoring and intelligent shut-off |
US8197473B2 (en) * | 2009-02-20 | 2012-06-12 | Vivant Medical, Inc. | Leaky-wave antennas for medical applications |
US8202270B2 (en) * | 2009-02-20 | 2012-06-19 | Vivant Medical, Inc. | Leaky-wave antennas for medical applications |
US8118808B2 (en) * | 2009-03-10 | 2012-02-21 | Vivant Medical, Inc. | Cooled dielectrically buffered microwave dipole antenna |
US9277969B2 (en) * | 2009-04-01 | 2016-03-08 | Covidien Lp | Microwave ablation system with user-controlled ablation size and method of use |
US10045819B2 (en) * | 2009-04-14 | 2018-08-14 | Covidien Lp | Frequency identification for microwave ablation probes |
US8463396B2 (en) * | 2009-05-06 | 2013-06-11 | Covidien LLP | Power-stage antenna integrated system with high-strength shaft |
US8216227B2 (en) * | 2009-05-06 | 2012-07-10 | Vivant Medical, Inc. | Power-stage antenna integrated system with junction member |
US8353903B2 (en) * | 2009-05-06 | 2013-01-15 | Vivant Medical, Inc. | Power-stage antenna integrated system |
US8292881B2 (en) * | 2009-05-27 | 2012-10-23 | Vivant Medical, Inc. | Narrow gauge high strength choked wet tip microwave ablation antenna |
US8834460B2 (en) * | 2009-05-29 | 2014-09-16 | Covidien Lp | Microwave ablation safety pad, microwave safety pad system and method of use |
US8235981B2 (en) * | 2009-06-02 | 2012-08-07 | Vivant Medical, Inc. | Electrosurgical devices with directional radiation pattern |
US8552915B2 (en) * | 2009-06-19 | 2013-10-08 | Covidien Lp | Microwave ablation antenna radiation detector |
US8334812B2 (en) * | 2009-06-19 | 2012-12-18 | Vivant Medical, Inc. | Microwave ablation antenna radiation detector |
US20100331834A1 (en) | 2009-06-29 | 2010-12-30 | Vivant Medical,Inc. | Ablation Probe Fixation |
US7863984B1 (en) * | 2009-07-17 | 2011-01-04 | Vivant Medical, Inc. | High efficiency microwave amplifier |
US8328799B2 (en) * | 2009-08-05 | 2012-12-11 | Vivant Medical, Inc. | Electrosurgical devices having dielectric loaded coaxial aperture with distally positioned resonant structure |
USD634010S1 (en) | 2009-08-05 | 2011-03-08 | Vivant Medical, Inc. | Medical device indicator guide |
US8328800B2 (en) * | 2009-08-05 | 2012-12-11 | Vivant Medical, Inc. | Directive window ablation antenna with dielectric loading |
USD613412S1 (en) | 2009-08-06 | 2010-04-06 | Vivant Medical, Inc. | Vented microwave spacer |
US9031668B2 (en) * | 2009-08-06 | 2015-05-12 | Covidien Lp | Vented positioner and spacer and method of use |
US8328801B2 (en) * | 2009-08-17 | 2012-12-11 | Vivant Medical, Inc. | Surface ablation antenna with dielectric loading |
US10828100B2 (en) * | 2009-08-25 | 2020-11-10 | Covidien Lp | Microwave ablation with tissue temperature monitoring |
US20110054459A1 (en) * | 2009-08-27 | 2011-03-03 | Vivant Medical, Inc. | Ecogenic Cooled Microwave Ablation Antenna |
US8409187B2 (en) * | 2009-09-08 | 2013-04-02 | Covidien Lp | Microwave antenna probe with high-strength ceramic coupler |
US9113925B2 (en) * | 2009-09-09 | 2015-08-25 | Covidien Lp | System and method for performing an ablation procedure |
US8355803B2 (en) * | 2009-09-16 | 2013-01-15 | Vivant Medical, Inc. | Perfused core dielectrically loaded dipole microwave antenna probe |
US9375273B2 (en) * | 2009-09-18 | 2016-06-28 | Covidien Lp | System and method for checking high power microwave ablation system status on startup |
US9095359B2 (en) * | 2009-09-18 | 2015-08-04 | Covidien Lp | Tissue ablation system with energy distribution |
US8394087B2 (en) * | 2009-09-24 | 2013-03-12 | Vivant Medical, Inc. | Optical detection of interrupted fluid flow to ablation probe |
US20110071516A1 (en) * | 2009-09-24 | 2011-03-24 | Tyco Healthcare Group Lp | System and Method for Controlling Electrosurgical Output |
US8282632B2 (en) * | 2009-09-28 | 2012-10-09 | Vivant Medical, Inc. | Feedpoint optimization for microwave ablation dipole antenna with integrated tip |
US8906007B2 (en) * | 2009-09-28 | 2014-12-09 | Covidien Lp | Electrosurgical devices, directional reflector assemblies coupleable thereto, and electrosurgical systems including same |
US8343145B2 (en) * | 2009-09-28 | 2013-01-01 | Vivant Medical, Inc. | Microwave surface ablation using conical probe |
US8545493B2 (en) * | 2009-09-29 | 2013-10-01 | Covidien Lp | Flow rate monitor for fluid cooled microwave ablation probe |
US9024237B2 (en) * | 2009-09-29 | 2015-05-05 | Covidien Lp | Material fusing apparatus, system and method of use |
US8568398B2 (en) | 2009-09-29 | 2013-10-29 | Covidien Lp | Flow rate monitor for fluid cooled microwave ablation probe |
US8876814B2 (en) * | 2009-09-29 | 2014-11-04 | Covidien Lp | Fluid cooled choke dielectric and coaxial cable dielectric |
US9113926B2 (en) * | 2009-09-29 | 2015-08-25 | Covidien Lp | Management of voltage standing wave ratio at skin surface during microwave ablation |
US8038693B2 (en) * | 2009-10-21 | 2011-10-18 | Tyco Healthcare Group Ip | Methods for ultrasonic tissue sensing and feedback |
US8568401B2 (en) * | 2009-10-27 | 2013-10-29 | Covidien Lp | System for monitoring ablation size |
US8382750B2 (en) * | 2009-10-28 | 2013-02-26 | Vivant Medical, Inc. | System and method for monitoring ablation size |
US8430871B2 (en) * | 2009-10-28 | 2013-04-30 | Covidien Lp | System and method for monitoring ablation size |
US20110118731A1 (en) * | 2009-11-16 | 2011-05-19 | Tyco Healthcare Group Lp | Multi-Phase Electrode |
US8394092B2 (en) * | 2009-11-17 | 2013-03-12 | Vivant Medical, Inc. | Electromagnetic energy delivery devices including an energy applicator array and electrosurgical systems including same |
US8764744B2 (en) * | 2010-01-25 | 2014-07-01 | Covidien Lp | System for monitoring ablation size |
US8568404B2 (en) | 2010-02-19 | 2013-10-29 | Covidien Lp | Bipolar electrode probe for ablation monitoring |
US8617153B2 (en) | 2010-02-26 | 2013-12-31 | Covidien Lp | Tunable microwave ablation probe |
USD681810S1 (en) | 2012-03-05 | 2013-05-07 | Covidien Lp | Ergonomic handle for ablation device |
US9370392B2 (en) | 2012-10-02 | 2016-06-21 | Covidien Lp | Heat-sensitive optical probes |
US9649146B2 (en) | 2012-10-02 | 2017-05-16 | Covidien Lp | Electro-thermal device |
US9522033B2 (en) | 2012-10-02 | 2016-12-20 | Covidien Lp | Devices and methods for optical detection of tissue contact |
US9668802B2 (en) | 2012-10-02 | 2017-06-06 | Covidien Lp | Devices and methods for optical detection of tissue contact |
US9901399B2 (en) | 2012-12-17 | 2018-02-27 | Covidien Lp | Ablation probe with tissue sensing configuration |
-
2009
- 2009-10-27 US US12/606,769 patent/US8568401B2/en active Active
-
2010
- 2010-10-27 EP EP20100014042 patent/EP2316371B1/en active Active
- 2010-10-27 JP JP2010240441A patent/JP5580168B2/en active Active
-
2013
- 2013-10-28 US US14/064,846 patent/US8894641B2/en active Active
-
2014
- 2014-07-10 JP JP2014142388A patent/JP2015006370A/en active Pending
- 2014-11-04 US US14/532,317 patent/US10004559B2/en active Active
-
2016
- 2016-07-21 JP JP2016143051A patent/JP6272407B2/en active Active
-
2017
- 2017-12-28 JP JP2017253410A patent/JP2018047350A/en active Pending
-
2018
- 2018-06-26 US US16/018,855 patent/US20180296266A1/en not_active Abandoned
Patent Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20040215183A1 (en) * | 1995-02-22 | 2004-10-28 | Medtronic, Inc. | Apparatus and method for creating, maintaining, and controlling a virtual electrode used for the ablation of tissue |
US20020077627A1 (en) * | 2000-07-25 | 2002-06-20 | Johnson Theodore C. | Method for detecting and treating tumors using localized impedance measurement |
Also Published As
Publication number | Publication date |
---|---|
EP2316371B1 (en) | 2014-03-05 |
US20150126991A1 (en) | 2015-05-07 |
US8568401B2 (en) | 2013-10-29 |
JP2011092715A (en) | 2011-05-12 |
JP5580168B2 (en) | 2014-08-27 |
US20140052124A1 (en) | 2014-02-20 |
JP2018047350A (en) | 2018-03-29 |
US10004559B2 (en) | 2018-06-26 |
JP2016179386A (en) | 2016-10-13 |
US20110098695A1 (en) | 2011-04-28 |
JP2015006370A (en) | 2015-01-15 |
US8894641B2 (en) | 2014-11-25 |
EP2316371A1 (en) | 2011-05-04 |
JP6272407B2 (en) | 2018-01-31 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US20180296266A1 (en) | System and method for monitoring ablation size | |
US10874459B2 (en) | System and method for monitoring ablation size | |
US10327845B2 (en) | System and method for monitoring ablation size | |
EP2361583B1 (en) | System for monitoring ablation size | |
US10213256B2 (en) | System and method for monitoring ablation size |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
STPP | Information on status: patent application and granting procedure in general |
Free format text: DOCKETED NEW CASE - READY FOR EXAMINATION |
|
AS | Assignment |
Owner name: VIVANT MEDICAL LLC, COLORADO Free format text: CHANGE OF NAME;ASSIGNOR:VIVANT MEDICAL, INC.;REEL/FRAME:047337/0844 Effective date: 20121226 Owner name: VIVANT MEDICAL, INC., COLORADO Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:BRANNAN, JOSEPH D.;REEL/FRAME:047324/0049 Effective date: 20091021 Owner name: COVIDIEN LP, MASSACHUSETTS Free format text: MERGER;ASSIGNOR:VIVANT MEDICAL LLC;REEL/FRAME:047324/0091 Effective date: 20121228 Owner name: COVIDIEN LP, MASSACHUSETTS Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:VIVANT MEDICAL LLC;REEL/FRAME:047332/0178 Effective date: 20121228 |
|
STPP | Information on status: patent application and granting procedure in general |
Free format text: NON FINAL ACTION MAILED |
|
STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION |