WO2002082993A1 - Apparatus and method for delivering ablative laser energy and determining the volume of tumor mass destroyed - Google Patents
Apparatus and method for delivering ablative laser energy and determining the volume of tumor mass destroyed Download PDFInfo
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- WO2002082993A1 WO2002082993A1 PCT/US2002/011452 US0211452W WO02082993A1 WO 2002082993 A1 WO2002082993 A1 WO 2002082993A1 US 0211452 W US0211452 W US 0211452W WO 02082993 A1 WO02082993 A1 WO 02082993A1
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- tumor mass
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/06—Devices, other than using radiation, for detecting or locating foreign bodies ; determining position of probes within or on the body of the patient
-
- 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
- A61B18/20—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 laser
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/06—Devices, other than using radiation, for detecting or locating foreign bodies ; determining position of probes within or on the body of the patient
- A61B5/061—Determining position of a probe within the body employing means separate from the probe, e.g. sensing internal probe position employing impedance electrodes on the surface of the body
- A61B5/064—Determining position of a probe within the body employing means separate from the probe, e.g. sensing internal probe position employing impedance electrodes on the surface of the body using markers
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/06—Radiation therapy using light
- A61N5/0601—Apparatus for use inside the body
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B2017/00017—Electrical control of surgical instruments
- A61B2017/00022—Sensing or detecting at the treatment site
- A61B2017/00084—Temperature
-
- 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
-
- 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
- A61B18/20—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 laser
- A61B2018/2005—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 laser with beam delivery through an interstitially insertable device, e.g. needle
-
- 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
- A61B18/20—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 laser
- A61B2018/206—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 laser the laser light passing along a liquid-filled conduit
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B90/00—Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
- A61B90/06—Measuring instruments not otherwise provided for
- A61B2090/063—Measuring instruments not otherwise provided for for measuring volume
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/01—Measuring temperature of body parts ; Diagnostic temperature sensing, e.g. for malignant or inflamed tissue
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/04—Positioning of patients; Tiltable beds or the like
- A61B6/0407—Supports, e.g. tables or beds, for the body or parts of the body
- A61B6/0414—Supports, e.g. tables or beds, for the body or parts of the body with compression means
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/50—Clinical applications
- A61B6/502—Clinical applications involving diagnosis of breast, i.e. mammography
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/06—Measuring blood flow
Definitions
- Percutaneous in situ or on-site treatment of malignant breast tumors by laser therapy is being developed in part due to the fact that breast cancer is being detected at earlier stages because of the increasing number of women receiving mammograms annually. If breast cancer and other cancers or tumors are detected in early development, the tumor can be effectively treated using an ablative agent such as laser energy.
- the apparatus of the '396 Patent includes a probe having a thin metallic cannula for insertion into a tumor mass, a laser for generating light having a chosen wavelength and intensity, and an optical fiber for receiving and transmitting the laser light to the tumor mass, whereby the optical fiber is inserted into the carinula such that a chosen physiologically acceptable fluid can flow coaxially between the cannula and the optical fiber.
- a heat sensing member is inserted adjacent into the tumor mass for monitoring the tumor temperature.
- the devitalized tumor is gradually cleared by the body immune system and within six months is replaced with a scar.
- the treatment of tumors and in particular the specific treatment of breast tumors is generally known to be more difficult due to the fact that it is difficult to determine the three dimensional boundaries of the tumor, and thus, difficult to determine when all ofthe tumor has been destroyed.
- tumor mass identification teclmiques for determining the size and outer boundaries of a tumor mass.
- conventional identification techniques that have been employed in combination with laser therapy are magnetic resonance imaging, radiographic and sonographic techniques.
- coordinates identifying the actual size of the tumor mass are determined by using stereotactic techniques or the like.
- markers may be placed in a 0.5-1.0 cm zone of "normal” tissue to demarcate the zone in which the tumor extension may exist.
- This ring of "normal” tissue is equivalent to a cuff of tissue engulfing the tumor removed during conventional surgery (i.e., a lumpectomy).
- the boundaries of the ring surrounding the tumor are marked at 3, 6, 9 and 12 o'clock locations by inserting metal markers through a needle.
- the insertion points are precisely determined by known stereotactic technique using a commercially available stereotactic table.
- Such marker elements are the subject of U.S. Patent No. 5,853,366 ("the '366 Patent”) issued to Dowlatshahi is directed to a marker element for interstitial treatment.
- the '366 Patent discloses a marker element that can be positioned wholly within the body of a patient by utilizing a guide member having a guide path so as to mark a tumor mass of interest.
- the marker element is made of a radiopaque material which includes any material that is capable of being detected by conventional radiographic, sonographic or magnetic teclmiques.
- the present invention recognizes the above described problem, that is, to provide a non-cutting treatment for cancer and in particular for breast cancer that can be relied upon to determine when the entire tumor is effectively destroyed. There is accordingly a need for a non-cutting breast cancer therapy which addresses this problem and the problems arising from the difficulty in deten ning whether the tumor is completely destroyed.
- the present invention solves the above problems by providing an apparatus and method for determining a volume of tumor mass (such as breast cancer) destruction in tissue mass (such as breast tissue) within the body of a patient such that a graphical representation ofthe destroyed mass can be preferably superimposed onto an image of the actual tumor mass whereby the destruction of tumor mass can be visually monitored in real-time.
- a volume of tumor mass such as breast cancer
- tissue mass such as breast tissue
- the preferred embodiment of this invention is described in conjunction with breast tissue and breast cancer or tumors, although it should be appreciated that the present invention may be adapted to be implemented for other tumor or cancer treatment.
- the preferred embodiment of the present invention is also implemented with a patient positioned on a commercially available stereotactic table.
- the invention may alternatively be implemented using ultrasound and magnetic resonance imaging (MRI) techniques, provided that the tissue mass such as the breast is immobilized and the target is fixed.
- the apparatus of one embodiment of the present invention preferably includes a laser gun.
- the laser gun is adapted to receive a laser probe having a temperature sensor thereon and a temperature probe having a series of temperature detectors thereon.
- the laser gun inserts the laser probe into the tumor mass to facilitate providing an effective amount of laser radiation and measuring the tumor temperature at the application point ofthe laser.
- the gun also subsequently inserts the temperature probe into the body preferably in close proximity ofthe tumor mass.
- the temperature probe measures the body or tissue temperature at various locations in proximity ofthe tumor mass during interstitial laser therapy.
- the laser probe and temperature probe preferably include position marks to enable the operator to precisely position and determine the position ofthe probes relative to each other.
- the apparatus preferably includes a computer control system that is electrically connected to the laser gun and its components, namely, the laser probe and sensor and the temperature probe and detectors.
- the computer control system determines the volume of tumor mass destroyed by utilizing operational data, such as, the distance between the temperature sensors, temperature data, that the control system receives from the laser probe and temperature probe.
- the computer control system calculates the volume of tumor mass destroyed at any given time during the interstitial laser therapy based upon the tumor mass temperature and the body or tissue mass temperature surrounding the tumor mass. As the computer control system calculates the volume of tumor mass destroyed, the computer control system displays sequential graphical representations of the amount of destroyed tumor mass which is superimposed onto an image of the actual tumor mass in real-time.
- This graphic display thereby enables doctors to visually monitor the amount of tumor mass destroyed in real-time during the interstitial laser therapy such that the user can determine when the tumor mass destruction is effectively complete. It is therefore an advantage ofthe present invention to provide an apparatus and method for calculating the volume of tumor mass destruction such that a graphic representation ofthe destroyed tumor mass can be displayed.
- FIG. 1A is a perspective view of the apparatus of the present invention for determining the volume of tumor mass destroyed.
- Fig. IB is a perspective view of the apparatus of the present invention which illustrates the laser gun.
- Fig. 2A is a schematic diagram of the laser probe and temperature probe prior to insertion into the tissue mass or body containing the tumor mass.
- Fig. 2B is a schematic diagram of the laser probe and temperature probe inserted into the tissue mass containing the tumor mass.
- Fig. 3 is a schematic diagram of the laser probe and temperature probe illustrating the relationship of the volume of tumor mass destroyed with respect to the temperature sensor ofthe laser probe and the temperature detectors of the temperature probe.
- Figs. 4A to 4C illustrate the graphically superimposed tumor mass destruction zone at a beginning, subsequent and final stages of laser therapy for visual real-time monitoring ofthe destruction ofthe tumor mass.
- Figs. 4D to 4H illustrate alternative graphical representations ofthe tumor mass destruction zone at begnining, subsequent and final stages of laser therapy for visual real-time monitoring ofthe destruction ofthe tumor mass.
- Figs. 41 and 4J illustrate a further alternative graphical bar representation ofthe temperature at Tc, Tl, T2, T3, T4 and T5 at different stages of the destruction of the tumor mass.
- Figs. 5A, 5B and 5C illustrate blood flow within the tumor mass and tissue mass surrounding the tumor mass before and after treatment as measured by color doppler ultrasound.
- Fig. 5A illustrates blood flow prior to treatment without the aid of a contrasting agent.
- Fig. 5B illustrates blood flow prior to treatment with the aid of a contrasting agent.
- Fig. 5C illustrates the loss of blood flow after treatment.
- Fig. 6 is a photograph that illustrates an actual tumor mass destroyed from laser therapy ofthe present invention.
- the present invention provides a graphical display or representation of the volume of destroyed tumor mass by determining the volume of destroyed tumor mass based on the relative temperatures of the tumor mass and temperatures of tissue mass surrounding the tumor mass as described in detail below.
- This display preferably provides doctors or other operators with real-time visual monitoring ofthe destruction of tumor mass so as to determine when the destruction of the entire tumor mass is effectively complete.
- the present invention monitors the temperature within and in close proximity to the tumor mass by utilizing a temperature sensor of the laser probe and a separate temperature probe having a number of temperature sensors or detectors.
- the temperature sensor and temperature probe provide temperature data for determining the volume of destroyed tumor mass, and thus, for providing the real-time graphical display ofthe destroyed tumor mass.
- the temperature probe To calculate the destroyed tumor mass volume, the temperature probe must be positioned correctly relative to the temperature sensor and the relative distances therebetween must be accurately determined.
- the present invention utilizes a number of position marks located on the temperature probe and laser probe for positioning and for determining the relative positioning between the temperature detector and the laser probe as discussed below.
- the present invention preferably includes a laser gun 10 including a probe holder 12 employed during interstitial laser therapy.
- the probe holder 12 is adapted to receive a laser probe 14 and a temperature probe 16.
- the laser probe 14 and temperature probe 16 are removably inserted in and extend from the probe holder.
- the laser probe 14 and the temperature probe 16 are held in fixed position relative to each other by the gun.
- the positioning of the laser probe 14 and temperature probe 16 may be manual or computer controlled in accordance with the present invention.
- the laser probe 14 includes a temperature sensor 15 and is adapted to receive an optical fiber 18 connected to a laser source 20 which is connected to a computer control system 22.
- the control system 22 is preferably connected to the temperature probe 16 and a temperature sensor 15 of the laser probe 14 via a temperature control device 24 so as to facilitate electrical connection with the computer control system 22.
- the laser probe 14 and temperature probe 16 can have separate control systems each connected to a central computer control system (not shown).
- the laser probe 14 includes a thin metallic cannula for insertion into the tumor mass and an optical fiber for receiving and transmitting the laser light or radiation to the tumor mass, whereby the optical fiber is inserted into the camiula such that a chosen physiologically acceptable fluid or anesthetic agent can flow between the cannula and the optical fiber as described in the '396 Patent which is herein incorporated by reference as discussed above.
- the thin metallic camiula was approximately 18 centimeters in length and made from stainless steel ranging from 16 gauge to 18 gauge, but preferably 16 gauge.
- the optical or laser fiber is a quartz fiber ranging from 400 nanometers (nm) to 600 nm in diameter with a spherical tip. The optical fiber is commercially available, for example, from SURGIMED in Woodland, Texas.
- any suitable fluid pump 26 can be utilized to deliver the fluid such that the central temperature of the tumor does not exceed 100°C or fall below 60°C during laser therapy.
- the fluid can be delivered at a rate ranging from 0.5 milliliters/minute (ml/min) to 2.0 ml/min.
- the laser source 20 generates and supplies an effective amount of laser radiation to the laser probe 14.
- the laser source 20 is preferably a diode laser.
- the laser source 20 is a semiconductor 805 -nanometer diode laser that is commercially available, for example, from Diomed in Cambridge, England.
- the present invention is not limited to the use of a diode laser and can utilize a variety of different and suitable laser sources.
- the laser probe 14 also includes a temperature sensor 15 as previously discussed.
- the temperature sensor 15 is employed to effectively measure a temperature of the center of the tumor mass as the tumor mass is destroyed.
- the temperature sensor 15 is preferably attached directly by soldering or other like attachment mechanism to the laser probe 14 so as to measure the tumor mass temperature at a distal end 28 of the laser probe 14, preferably located at a center region ofthe tumor mass.
- the distal end 30 of the temperature probe 16 is inserted into the body within the tissue mass ofthe body region that is in proximity of (i.e., preferably 1.0 cm away) and surrounds the tumor mass.
- the temperature probe 16 includes a series of temperature detectors 32 or sensors that are positioned at various distances or intervals (i.e., preferably 0.5 cm) along the temperature probe, h a preferred embodiment, the temperature probe 16 is made from stainless steel ranging from 16 gauge to 20 gauge, preferably 16 gauge. As further illustrated in Fig. 3, the temperature detectors 32 of the temperature probe 16 are positioned at Tl, T2, T3, T4 and T5. Based on this configuration, tissue mass temperature measurements are taken at various distances away from the tumor mass surface. This temperature data is utilized in conjunction with the relative distances ofthe temperature sensors to calculate the volume of tumor mass destroyed, and therefore is utilized to determine when the entire tumor mass is effectively destroyed as discussed below.
- the temperature probe 16 and laser probe 14 include a number of position marks 34 in order to determine the relative positions of the temperature probe 16 and laser probe 14.
- the position marks 34 are preferably evenly spaced apart along a portion of a length of the temperature probe 16 and along a portion of the length of the laser probe 14 at a preferable distance of 0.5 cm.
- the present invention is not limited to this distance and can include position marks spaced apart at a variety of different positions. The operator can use these position marks to correctly position the laser probe and the temperature probe relative to the laser probe.
- the present invention preferably includes the computer control system 22 adapted to electronically connect to the laser gun 10 and its components, namely, the temperature probe and the laser probe 14 having the temperature sensor 15.
- the computer control system 22 receives data from the laser probe 14 and the temperature probe 16 as the tumor mass is heated and destroyed. The data is utilized to calculate the volume of tumor mass destroyed at any given point in time. This calculation is based upon the temperature data from the temperature probe 16 and temperature sensor 15.
- the computer control system 22 utilizes the destroyed tumor volume calculations for graphically depicting the volume of tumor mass destroyed (i.e., tumor mass destruction zone) on a display 36 connected to the computer control system 22.
- the laser gun 10 injects the laser probe 14 and temperature probe 16 into breast tissue 38 in order to destroy a tumor mass 40 located within the breast tissue 38 of a patient 41 lying on an examination table 42.
- the laser gun 10 is positioned on a stereotactic platform or table 44 wliich is utilized in a conventional manner to identify the actual location ofthe tumor mass 40 in the breast tissue 38 prior to insertion of the temperature probe 16 and laser probe 14 into the breast tissue 38.
- the stereotactic platform or table 44 is commercially available from LORAD/Trex Medical Stereoguide DSM of Danbury, Com ecticut. However, this identification can be performed using conventional radiographic, sonographic, thermo graphic, magnetic imaging or other like identification techniques.
- a number of marker elements 46 are preferably inserted into the breast tissue 38 in close proximity of the breast tumor 40.
- the marker elements 46 are utilized for marking the tumor mass 40 to be treated and to allow subsequent identification and observation of the treated area as further described in the '366 Patent herein incorporated by reference as previously discussed.
- the laser gun 10 can be configured to inject the laser probe 14 and temperature probe 16 into the breast tissue 38 at an optimal location relative to the tumor mass 40 in the breast tissue 38.
- the present invention utilizes a probe guide 48 to facilitate the insertion of the temperature probe 16 and laser probe 14 into the breast tissue 38.
- the positioning of the laser probe 14, temperature probe 16 and marker elements 46 relative to the positioning of the tumor mass 40 and tissue mass surrounding the tumor mass can be visually monitored on the display 36.
- the present invention utilizes a laser gun 10 to inject the laser probe 14 and temperature probe 16 into the tumor mass and tissue mass surrounding the tumor mass.
- the laser gun 10 can be made of any suitable material and be constructed in a variety of different configurations. One example of such configuration is illustrated in Fig. IB.
- the laser gun 10 is positioned on a guide mechanism 52 of the stereotactic table 44 which enables the laser gun 10 to be positioned prior to insertion of the laser probe and temperature probe.
- the laser gun 10 includes a housing 54 for the laser probe and temperature probe and probe holders 12 which can extend from the housing for each ofthe laser probe and temperature probe.
- the laser gun 10 further includes an alignment member 56 attached to the housing for aligning the laser gun prior to insertion.
- the laser gun 10 can also include an inserter member 58 attached to the housing for automatically inserting the laser probe and temperature probe.
- the laser gun 10 is connected to a control system 59 wliich includes a computer processing unit 60.
- the control system 58 operates to control and monitor the temperature probe and laser probe during laser therapy, such as controlling the laser source and fluid pump and monitoring the temperature.
- the laser probe 14 is first optimally inserted into the center of the tumor mass as shown in Fig. 2B.
- the temperature probe 16 is optimally inserted and positioned parallel to the laser probe 14 (i.e., preferably approximately 1 cm away from the laser probe) as further illustrated in Figs. 2A and 2B.
- the optimal locations of the temperature probe 16 and laser probe 14 are necessary to monitor a concentric zone of heat emitted from the tip of the laser probe during treatment. As discussed below, the ability to monitor the concentric heat patterns of the laser probe is necessary to effectively measure the volume of tumor mass destroyed during treatment.
- the present invention preferably utilizes the stereotactic technique in combination with the marker elements to monitor this positioning.
- the present invention further utilizes a plurality of position marks 34 located on each of the temperature probe 16 and laser probe 14 for monitoring the axial positioning of the laser probe 14 relative to the temperature probe 16.
- the position marks 34 are spaced apart at known distances, preferably 0.5 cm, along each of the temperature probe 16 and laser probe 14. Therefore, the position marks 34 are utilized to visually monitor the relative positioning of the laser probe 14 and temperature probe 16 such that manual adjustments in addition to computer automated adjustments can be made to the relative positioning ofthe laser probe 14 and temperature probe 16. As shown in Fig.
- the temperature probe 16 preferably includes a temperature detector T3 that contacts an outer surface of the tumor mass 40 to measure a temperature at this location.
- the remaining temperature detectors namely, Tl, T2, T4 and T5 are positioned at the distances (described above) from T3 along the temperature probe.
- Each temperature detector is also located at various radial distances from the temperature sensor Tc (i.e., the temperature at the center of the tumor mass) of the laser probe 14, namely, rl, r2, r3, r4 and r5.
- the radial distance between Tc and T3 i.e., r3 is known, that is, the axial distance between Tc and T3, preferably 1.0 cm.
- the tissue temperature surrounding the tumor relative to the temperature at the laser fiber tip i.e., Tc
- Tc the temperature detectors
- the temperature detectors such as Tl, T2, T3, T4 and T5
- rl 1.4 cm
- r2 1.10 cm
- r3 1.0 cm
- r4 1.10 cm
- r5 1.4 cm as previously discussed.
- the tumor mass 40 is destroyed in a region at and near Tc.
- the volume of tumor mass destroyed increases in correlation to an increase in the temperature as measured by T3. Therefore, the volume of tumor mass destroyed is effectively less than the volume corresponding to the spherical region having a radial distance of r3.
- the volume of tumor mass destroyed effectively corresponds to the volume of a spherical region having a radial distance of r3.
- the spherical shape of the destroyed tumor mass has been documented on rodent mammary tumors and thirty-six patients with breast cancer whose laser treated tumors were serially removed and sectioned by pathologists and reported.
- the laser treatment continues until the temperatures as measured by the other or outer temperature detectors, namely, Tl, T2, T4 and T5, reach or increase to the tumor mass destruction temperature, preferably 60°C.
- the tumor mass is effectively destroyed within the volume ofthe spherical region having a radial distance associated with the outer temperature detectors, namely, rl, r2, r4 and r5.
- the laser treatment ends when a temperature as measured by the outermost temperature detector(s), such as Tl and T5, increases to the tumor mass destruction temperature, preferably 60°C.
- the amount of laser energy which is necessary to destroy the tumor mass and the tissue mass surrounding the tumor mass can also be determined. Based on previous studies conducted by the inventor, the destruction of approximately 1 cm 3 of tumor mass and/or tissue mass surrounding the tumor mass requires approximately 2500 Joules (J) of laser energy.
- the present invention is not limited to the number, type, positions, and locations of the temperature detectors. A variety of locations and number of detectors may be utilized depending, for example, on the tumor treatment conditions, such as, the type and location ofthe tumor.
- the temperature detectors are positioned to effectively monitor the destruction of tumor mass to a radial distance from the actual tumor mass associated with the outer temperature detectors (i.e., Tl and T5).
- the present invention is not limited to the tumor mass destruction temperature.
- a variety of different temperatures may be utilized to correspond to the tumor mass destruction temperature depending on the tumor treatment conditions as described above.
- the preferred tumor mass destruction temperature is at least 60°C.
- the computer control system utilizes the tumor mass destruction calculation(s) as described above to provide a graphic display 62 or representation of the destroyed tumor mass that is preferably superimposed onto an image of the actual tumor mass taken prior to treatment as illustrated in Fig. 4A.
- the graphic display 62 of the destroyed tumor mass is preferably displayed as a circular (2-D) or spherical (3-D) symbol.
- the marker elements are also graphically displayed in addition to the tumor mass.
- the display 62 illustrates the laser probe 14 and temperature probe 16 after insertion into the breast tissue.
- the tip 64 of the laser probe 14 is centrally located within the tumor mass 40, and the temperature probe 16 is positioned relative to the laser probe 14 as previously discussed.
- the temperature detector at T3 measures a tumor mass destruction temperature (i.e., preferably 60°C).
- the destroyed tumor mass symbol 66 appears as illustrated in the display of Fig. 4B.
- the destroyed tumor mass symbol 67 expands to include the destroyed tumor mass region associated with Tl and T5 as shown in Fig. 4C.
- the tumor mass destruction symbol extends outwardly from the actual image of the tumor mass by a distance associated with the location of the outer temperature detectors of the temperature probe (i.e., Tl and T5). At this distance, the tumor mass destruction is effectively complete as further illustrated in Fig. 4C. This distance ranges from about 0.25 cm to about 0.75 cm, preferably ranging from about 0.4 cm to about 0.5 cm.
- the graphic display ofthe present invention provides a real-time visual monitoring of the destruction of tumor mass in contrast to known displays that only illustrate the temperature at various locations of the tumor mass by a conventional bar graph.
- FIG. 4D illustrates the tumor without any destruction zone.
- Figs. 4E, 4F, 4G and 4H illustrates the destruction zone increasing in size to expand beyond the tumor zone. It should be appreciated that different cross hatching, shading and graphical images can be used to graphically illustrate the tumor mass and the destruction zone. It should also be appreciated that different colors can be graphically used to illustrate the tumor mass and the destruction zone.
- Figs. 41 and 4J illustrate a bar graph wliich is preferably also provided to the operator of the system.
- the bar graphs show the temperature at Tc, Tl, T2, T3, T4 and T5 at different points in time.
- the temperature at Tc is much greater than the temperature at T3, which is greater than the temperature at T2 and T4, which is greater than the temperature at Tl and T5.
- the bar graph changes to a point in time as illustrated in Fig. 4J.
- the areas at Tl and T5 are above the tumor mass destruction temperature which is preferably 60°C. Therefore, the operator knows that the mass has been destroyed in addition to the graphical representations described above.
- the present invention utilizes a blood circulation test in combination with real-time visual monitoring to determine when the destruction of the entire tumor mass is effectively complete.
- Any suitable blood circulation test can be utilized.
- contrast-enhanced color doppler ultrasound is the preferred technique that utilizes a suitable contrasting agent and a suitable transducer ultrasound for observing blood with color as it circulates in the tumor mass and tissue mass (i.e., breast tissue) surrounding the tumor mass.
- the blood circulation test is conducted before and after treatment and the results are compared to determine whether the tumor mass was effectively destroyed.
- Any suitable transducer and contrasting agent may be utilized.
- the transducer ultrasound is a 7.5 MHz linear array transducer ultrasound that is commercially available from ATL in Bothel, Washington.
- the contrasting agent is preferably a sonicated albumin-based agent, that is, an albumin-based material having gas-injected bubbles. It should be appreciated that the reflection of sound waves from the bubbles within the albumin- based material produces a color response indicative of blood flow or circulation.
- the contrasting agent is OPTISON which is a commercially available product from Mallinkrodt of St. Louis, Missouri.
- an effective amount of the contrasting agent is preferably injected into a vein.
- the contrasting agent is utilized to enhance the image of blood circulation that results from the color doppler ultrasound technique.
- the effectiveness of the contrasting agent is shown by comparing the color doppler ultrasound blood flow images of Fig. 5 A and 5B.
- the contrasting agent was utilized to produce the blood flow image of Fig. 5B and not Fig. 5 A. By comparing these figures, it is evident that the blood flow image of Fig. 5B is more enhanced than the blood flow image of Fig. 5 A.
- the contrast-enhanced color doppler ultrasound measured a substantial amount of blood flow within the tumor mass and tissue mass surrounding the tumor mass.
- the contrasting agent is again injected to observe blood flow in and around the tumor mass.
- there was effectively no blood flow within the tumor mass and surrounding area as measured by the above- described ultrasound technique as shown in Fig. 5C. This indicates that the tumor mass and tissue mass surrounding the tumor mass was effectively destroyed. If the tumor mass and the surrounding tissue mass has been destroyed, blood circulation in this treated region effectively cannot be observed by color doppler ultrasound.
- a comparative analysis between the results of the blood circulation test before and after treatment is utilized to make the determination as to whether the entire tumor mass is destroyed.
- This change in blood circulation in and around the tumor mass can also be observed by injecting an effective amount ofthe contrasting agent into the vein during laser therapy.
- This provides real-time monitoring of the blood circulation within the tumor mass and tissue mass surrounding the tumor mass during laser treatment. As more and more ofthe tumor mass and surrounding tissue mass is destroyed, less blood circulates through this region.
- the blood circulation test such as the color doppler ultrasound
- a graphical representation of the results of the color doppler ultrasound can be continuously monitored during laser therapy.
- the graphical representation can be displayed on a separate display or can be superimposed onto the actual image of the tumor mass during laser therapy.
- the graphical representation provides further real-time monitoring of tumor destruction before the patient is removed from the table. Additional laser treatment can be delivered if a portion of the targeted tissue exhibits blood flow suggesting viability. It should be appreciated that the graphical representation can be configured in any suitable way such that the blood flow circulation can be monitored.
- FIG. 6 An actual tumor mass that has been destroyed during laser therapy of the present invention is illustrated in Fig. 6.
- the void region represents the region where the tumor mass and surrounding tissue mass were destroyed by laser therapy. As shown in Fig. 6, the void region is effectively circular in shape and has an approximate diameter of 2.5 to 3.0 cm.
- Fig. 6 illustrates a cut section of a laser treated breast tumor. The red ring is the inflammatory zone and the tissue within it is destroyed. The diameter of this ring corresponds to the diameter of the avascular zone seen by color Doppler ultrasound in Fig. 5 C .
- the present invention also provides a method for determining the volume of tumor mass destroyed.
- the method preferably includes the step of providing a laser gun.
- the laser gun further includes a laser probe and temperature probe as detailed above.
- the laser probe and temperature probe are inserted into the body of the patient such that the laser probe is inserted into the tumor mass and the temperature probe is inserted into the tissue mass in proximity to the tumor mass.
- An effective amount of laser radiation is generated and directed into the tumor mass through the laser probe.
- the temperature sensor ofthe laser probe measures the tumor mass temperature within the tumor mass.
- the temperature probe measures the tissue temperature of tissue mass surrounding the tumor mass at various positions along the temperature probe.
- the computer control system is preferably electronically connected to the laser gun and its components, namely the laser probe, the temperature sensor ofthe laser probe, and the temperature probe, and a fluid pump.
- the computer control system receives temperature and laser data from the temperature and laser probes for determining or calculating a volume of tumor mass destruction as detailed above.
- the computer (or operator) adjusts the fluid flow delivered by the fluid pump so that the central temperature of the tumor, i.e., Tc, does not exceed 100°C or fall below 60°C during laser therapy.
- the computer control system utilizes this calculation to create a display that graphically superimposes the destroyed tumor mass onto the image ofthe actual tumor mass.
- the doctor can visually monitor the destruction of tumor mass under real-time so as to determine when the destruction of tumor mass is effectively complete as detailed above.
- the method ofthe present invention includes the step of identifying the tumor mass prior to insertion of the laser gun into the tumor mass.
- the identification step is performed using conventional radiographic, sonographic or magnetic imaging teclmiques.
- coordinates identifying the actual location of the tumor mass are determined using stereotactic teclmiques or the like as previously discussed.
- the present invention utilizes a blood circulation test, such as color doppler ultrasound, before and after treatment to provide further evidence when the entire tumor mass is effectively destroyed as previously discussed.
- the blood circulation test can also be utilized during laser therapy to provide further real-time monitoring ofthe tumor mass destruction as further discussed above. It should be appreciated that the present invention is not limited to interstitial laser therapy, and particularly, interstitial laser therapy for the destruction of a breast tumor. The present invention may apply to a variety of different non-surgical treatments for the destruction of a variety of different tumor masses.
Abstract
Description
Claims
Priority Applications (9)
Application Number | Priority Date | Filing Date | Title |
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AU2002303314A AU2002303314B2 (en) | 2001-04-13 | 2002-04-12 | Apparatus and method for delivering ablative laser energy and determining the volume of tumor mass destroyed |
DE60221371T DE60221371T2 (en) | 2001-04-13 | 2002-04-12 | DEVICE FOR DELIVERING ABLATIVE LASER ENERGY AND DETERMINING THE VOLUME OF DESTROYED TUMOR MASS |
CA2443739A CA2443739C (en) | 2001-04-13 | 2002-04-12 | Apparatus and method for delivering ablative laser energy and determining the volume of tumor mass destroyed |
EP02731333A EP1377210B1 (en) | 2001-04-13 | 2002-04-12 | Apparatus for delivering ablative laser energy and determining the volume of tumor mass destroyed |
BRPI0208877-0A BR0208877B1 (en) | 2001-04-13 | 2002-04-12 | apparatus for determining a destroyed tumor mass volume and system for providing ablative laser energy to a tumor mass. |
JP2002580802A JP4338976B2 (en) | 2001-04-13 | 2002-04-12 | Apparatus and method for supplying ablative laser energy and determining the volume of a destroyed tumor mass |
MXPA03009295A MXPA03009295A (en) | 2001-04-13 | 2002-04-12 | Apparatus and method for delivering ablative laser energy and determining the volume of tumor mass destroyed. |
NZ529478A NZ529478A (en) | 2001-04-13 | 2002-04-12 | Apparatus and method for delivering ablative laser energy and determining the volume of tumor mass destroyed |
AU2006203717A AU2006203717B2 (en) | 2001-04-13 | 2006-08-25 | Apparatus and method for delivering ablative laser energy and determining the volume of tumor mass destroyed |
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EP (1) | EP1377210B1 (en) |
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Families Citing this family (77)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6603988B2 (en) * | 2001-04-13 | 2003-08-05 | Kelsey, Inc. | Apparatus and method for delivering ablative laser energy and determining the volume of tumor mass destroyed |
US7363071B2 (en) | 1999-05-26 | 2008-04-22 | Endocare, Inc. | Computer guided ablation of tissue using integrated ablative/temperature sensing devices |
US8083736B2 (en) | 2000-03-06 | 2011-12-27 | Salient Surgical Technologies, Inc. | Fluid-assisted medical devices, systems and methods |
US8048070B2 (en) | 2000-03-06 | 2011-11-01 | Salient Surgical Technologies, Inc. | Fluid-assisted medical devices, systems and methods |
ES2643763T3 (en) | 2000-03-06 | 2017-11-24 | Salient Surgical Technologies, Inc. | Fluid supply system and controller for electrosurgical devices |
US6558385B1 (en) | 2000-09-22 | 2003-05-06 | Tissuelink Medical, Inc. | Fluid-assisted medical device |
US6689131B2 (en) | 2001-03-08 | 2004-02-10 | Tissuelink Medical, Inc. | Electrosurgical device having a tissue reduction sensor |
US7811282B2 (en) * | 2000-03-06 | 2010-10-12 | Salient Surgical Technologies, Inc. | Fluid-assisted electrosurgical devices, electrosurgical unit with pump and methods of use thereof |
US8256430B2 (en) | 2001-06-15 | 2012-09-04 | Monteris Medical, Inc. | Hyperthermia treatment and probe therefor |
US20050143791A1 (en) * | 2001-07-09 | 2005-06-30 | Stuart Hameroff | Process of treating a cell |
SE522697C2 (en) * | 2001-11-14 | 2004-03-02 | Spectracure Ab | Therapy and diagnostic systems with distributors for distribution of radiation |
BR0312430A (en) | 2002-06-19 | 2005-04-26 | Palomar Medical Tech Inc | Method and apparatus for treating skin and subcutaneous conditions |
EP1572020A4 (en) | 2002-10-29 | 2006-05-03 | Tissuelink Medical Inc | Fluid-assisted electrosurgical scissors and methods |
US7041109B2 (en) * | 2002-12-12 | 2006-05-09 | Kelsey, Inc. | Apparatus and method for interstitial laser therapy of small breast cancers and adjunctive therapy |
EP1493389A1 (en) * | 2003-07-01 | 2005-01-05 | Siemens Aktiengesellschaft | Method of and device for forming x-ray images of the focal region of a lithotripter |
JP4328586B2 (en) * | 2003-09-02 | 2009-09-09 | キヤノン株式会社 | Radiation image connection processing method, radiation image connection processing apparatus, computer program, and computer-readable recording medium |
US7270656B2 (en) | 2003-11-07 | 2007-09-18 | Visualase, Inc. | Cooled laser fiber for improved thermal therapy |
SE0303124D0 (en) * | 2003-11-25 | 2003-11-25 | Elekta Instr Ab | An apparatus for controlled directional monitoring and destruction of tissue |
US7727232B1 (en) | 2004-02-04 | 2010-06-01 | Salient Surgical Technologies, Inc. | Fluid-assisted medical devices and methods |
EP1720608B1 (en) | 2004-02-12 | 2010-11-17 | NeoVista, Inc. | Apparatus for intraocular brachytherapy |
US7445617B2 (en) * | 2004-05-10 | 2008-11-04 | Salient Surgical Technologies, Inc. | Temperature indicating devices and methods of use |
US20060000814A1 (en) * | 2004-06-30 | 2006-01-05 | Bo Gu | Laser-based method and system for processing targeted surface material and article produced thereby |
US7856985B2 (en) | 2005-04-22 | 2010-12-28 | Cynosure, Inc. | Method of treatment body tissue using a non-uniform laser beam |
SE0501078L (en) * | 2005-05-12 | 2006-11-13 | Spectracure Ab | A device for analyzing a fluid flow |
US20070016011A1 (en) * | 2005-05-18 | 2007-01-18 | Robert Schmidt | Instrument position recording in medical navigation |
CA2629648A1 (en) | 2005-11-15 | 2007-05-24 | Neovista Inc. | Methods and apparatus for intraocular brachytherapy |
DE102005056080B4 (en) * | 2005-11-24 | 2010-04-08 | Siemens Ag | Device for X-ray brachytherapy with a probe insertable into the interior of a body for X-ray brachytherapy |
WO2008003640A1 (en) * | 2006-07-04 | 2008-01-10 | Bracco Imaging S.P.A. | Device for localized thermal ablation of biological tissues, particularly tumoral tissues or the like |
JP5211044B2 (en) * | 2006-07-04 | 2013-06-12 | ブラッコ イメージング ソチエタ ペル アチオニ | Thermal excision device that excises local lesions such as tumor tissue with heat |
US7586957B2 (en) | 2006-08-02 | 2009-09-08 | Cynosure, Inc | Picosecond laser apparatus and methods for its operation and use |
GB2441789B (en) * | 2006-09-18 | 2012-03-28 | Angus Buchan Gordon | Use of a Tumour Volume Measuring Device |
US10179247B2 (en) * | 2007-02-05 | 2019-01-15 | Novian Health, Inc. | Interstitial laser therapy control system |
US8092507B2 (en) | 2007-02-05 | 2012-01-10 | Novian Health, Inc. | Interstitial energy treatment probe holders |
WO2008153999A1 (en) * | 2007-06-08 | 2008-12-18 | Cynosure, Inc. | Thermal surgery safety apparatus and method |
US9403029B2 (en) * | 2007-07-18 | 2016-08-02 | Visualase, Inc. | Systems and methods for thermal therapy |
CN101888813B (en) * | 2007-12-06 | 2012-12-12 | 皇家飞利浦电子股份有限公司 | Apparatus, a method and a computer program for applying energy to an object |
JP5489148B2 (en) * | 2007-12-28 | 2014-05-14 | ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー | Ultrasonic diagnostic equipment |
EP2227174B1 (en) | 2007-12-28 | 2019-05-01 | Salient Surgical Technologies, Inc. | Fluid-assisted electrosurgical device |
CN101960489A (en) | 2007-12-31 | 2011-01-26 | 真实成像有限公司 | Method, apparatus and system for analyzing thermal images |
WO2009118721A1 (en) * | 2008-03-28 | 2009-10-01 | Real Imaging Ltd. | Method apparatus and system for analyzing thermal images |
ITFI20080176A1 (en) * | 2008-09-15 | 2010-03-16 | Elesta S R L | "METHOD AND DEVICE FOR ECOGRAPHIC TREATMENT AND MONITORING THROUGH PERCUTANEOUS LASER ABLATION" |
US9254168B2 (en) | 2009-02-02 | 2016-02-09 | Medtronic Advanced Energy Llc | Electro-thermotherapy of tissue using penetrating microelectrode array |
JP5592409B2 (en) | 2009-02-23 | 2014-09-17 | サリエント・サージカル・テクノロジーズ・インコーポレーテッド | Fluid-assisted electrosurgical device and method of use thereof |
US8663210B2 (en) | 2009-05-13 | 2014-03-04 | Novian Health, Inc. | Methods and apparatus for performing interstitial laser therapy and interstitial brachytherapy |
IN2012DN01917A (en) | 2009-09-08 | 2015-07-24 | Salient Surgical Tech Inc | |
WO2011112991A1 (en) | 2010-03-11 | 2011-09-15 | Salient Surgical Technologies, Inc. | Bipolar electrosurgical cutter with position insensitive return electrode contact |
US20110295249A1 (en) * | 2010-05-28 | 2011-12-01 | Salient Surgical Technologies, Inc. | Fluid-Assisted Electrosurgical Devices, and Methods of Manufacture Thereof |
US9138289B2 (en) | 2010-06-28 | 2015-09-22 | Medtronic Advanced Energy Llc | Electrode sheath for electrosurgical device |
US8906012B2 (en) | 2010-06-30 | 2014-12-09 | Medtronic Advanced Energy Llc | Electrosurgical devices with wire electrode |
US8920417B2 (en) | 2010-06-30 | 2014-12-30 | Medtronic Advanced Energy Llc | Electrosurgical devices and methods of use thereof |
US9023040B2 (en) | 2010-10-26 | 2015-05-05 | Medtronic Advanced Energy Llc | Electrosurgical cutting devices |
US9427281B2 (en) | 2011-03-11 | 2016-08-30 | Medtronic Advanced Energy Llc | Bronchoscope-compatible catheter provided with electrosurgical device |
US9750565B2 (en) | 2011-09-30 | 2017-09-05 | Medtronic Advanced Energy Llc | Electrosurgical balloons |
US8870864B2 (en) | 2011-10-28 | 2014-10-28 | Medtronic Advanced Energy Llc | Single instrument electrosurgery apparatus and its method of use |
KR102183581B1 (en) | 2012-04-18 | 2020-11-27 | 싸이노슈어, 엘엘씨 | Picosecond laser apparatus and methods for treating target tissues with same |
CN104602638B (en) | 2012-06-27 | 2017-12-19 | 曼特瑞斯医药有限责任公司 | System for influenceing to treat tissue |
EP2973894A2 (en) | 2013-03-15 | 2016-01-20 | Cynosure, Inc. | Picosecond optical radiation systems and methods of use |
EP2799111A1 (en) * | 2013-04-30 | 2014-11-05 | Clinical Laserthermia Systems AB | Apparatus and method for controlling immunostimulating laser thermotherapy |
USD733873S1 (en) | 2013-05-07 | 2015-07-07 | Novian Health Inc. | Probe holder |
US10631914B2 (en) | 2013-09-30 | 2020-04-28 | Covidien Lp | Bipolar electrosurgical instrument with movable electrode and related systems and methods |
US20150265353A1 (en) | 2014-03-18 | 2015-09-24 | Monteris Medical Corporation | Image-guided therapy of a tissue |
WO2015143025A1 (en) | 2014-03-18 | 2015-09-24 | Monteris Medical Corporation | Image-guided therapy of a tissue |
US10675113B2 (en) | 2014-03-18 | 2020-06-09 | Monteris Medical Corporation | Automated therapy of a three-dimensional tissue region |
US10420608B2 (en) | 2014-05-20 | 2019-09-24 | Verily Life Sciences Llc | System for laser ablation surgery |
US9974599B2 (en) | 2014-08-15 | 2018-05-22 | Medtronic Ps Medical, Inc. | Multipurpose electrosurgical device |
US9956029B2 (en) | 2014-10-31 | 2018-05-01 | Medtronic Advanced Energy Llc | Telescoping device with saline irrigation line |
US10327830B2 (en) | 2015-04-01 | 2019-06-25 | Monteris Medical Corporation | Cryotherapy, thermal therapy, temperature modulation therapy, and probe apparatus therefor |
US11389227B2 (en) | 2015-08-20 | 2022-07-19 | Medtronic Advanced Energy Llc | Electrosurgical device with multivariate control |
US11051875B2 (en) | 2015-08-24 | 2021-07-06 | Medtronic Advanced Energy Llc | Multipurpose electrosurgical device |
US10888708B2 (en) | 2015-11-11 | 2021-01-12 | Qc, Llc | Phototherapy device with real-time morphologic feedback and guidance |
US10716612B2 (en) | 2015-12-18 | 2020-07-21 | Medtronic Advanced Energy Llc | Electrosurgical device with multiple monopolar electrode assembly |
US11172821B2 (en) * | 2016-04-28 | 2021-11-16 | Medtronic Navigation, Inc. | Navigation and local thermometry |
SG11202008151QA (en) | 2018-02-26 | 2020-09-29 | Cynosure Inc | Q-switched cavity dumped sub-nanosecond laser |
WO2020163854A1 (en) * | 2019-02-08 | 2020-08-13 | Emory University | Devices, systems, and methods for cryoablation |
JP7335439B2 (en) | 2019-10-28 | 2023-08-29 | ボストン サイエンティフィック ニューロモデュレイション コーポレイション | RF electrode cannula |
WO2021252122A1 (en) * | 2020-06-12 | 2021-12-16 | Medtronic Navigation, Inc. | System and method for correlating proton resonance frequency thermometry with tissue temperatures |
JP2023553834A (en) * | 2020-11-30 | 2023-12-26 | カオ グループ、インク. | Non-invasive cancer treatment using multi-wavelength laser |
Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5178148A (en) * | 1990-04-06 | 1993-01-12 | Technomed International | Method of automatically measuring the volume of a tumor or of a gland, in particular the prostate, a measuring device, and a method and apparatus constituting and application thereof |
US5569240A (en) * | 1990-06-08 | 1996-10-29 | Kelsey, Inc. | Apparatus for interstitial laser therapy |
US5620479A (en) * | 1992-11-13 | 1997-04-15 | The Regents Of The University Of California | Method and apparatus for thermal therapy of tumors |
Family Cites Families (110)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US1968997A (en) | 1932-05-21 | 1934-08-07 | Kenneth G Drucker | Device for the treatment of certain ailments |
US4305390A (en) | 1975-11-28 | 1981-12-15 | Massachusetts Institute Of Technology | Method for generating oxygen in an excited electronic state and inactivation of microorganisms |
US6603988B2 (en) * | 2001-04-13 | 2003-08-05 | Kelsey, Inc. | Apparatus and method for delivering ablative laser energy and determining the volume of tumor mass destroyed |
US4222375A (en) | 1978-03-10 | 1980-09-16 | Miguel Martinez | In vivo illumination system utilizing a cannula with a conical opening allowing a snap-fit with a conical lens and an aperture for flow of fluids and utilizing a housing with a spherical lens for focusing light onto fiber optics |
DE2826383A1 (en) | 1978-06-16 | 1979-12-20 | Eichler Juergen | Probe for laser surgery - is tubular and placed against or inserted in tissue, with or without heated end |
JPS55130640A (en) | 1979-03-30 | 1980-10-09 | Olympus Optical Co | Endoscope |
US4649151A (en) | 1982-09-27 | 1987-03-10 | Health Research, Inc. | Drugs comprising porphyrins |
US4961422A (en) * | 1983-01-21 | 1990-10-09 | Marchosky J Alexander | Method and apparatus for volumetric interstitial conductive hyperthermia |
US4773413A (en) | 1983-06-13 | 1988-09-27 | Trimedyne Laser Systems, Inc. | Localized heat applying medical device |
US4662368A (en) | 1983-06-13 | 1987-05-05 | Trimedyne Laser Systems, Inc. | Localized heat applying medical device |
US5019075A (en) | 1984-10-24 | 1991-05-28 | The Beth Israel Hospital | Method and apparatus for angioplasty |
US4616656A (en) | 1985-03-19 | 1986-10-14 | Nicholson James E | Self-actuating breast lesion probe and method of using |
US4776334A (en) | 1985-03-22 | 1988-10-11 | Stanford University | Catheter for treatment of tumors |
US4665927A (en) | 1985-07-22 | 1987-05-19 | Pat O. Daily | Intraoperative temperature probe |
US4681122A (en) | 1985-09-23 | 1987-07-21 | Victory Engineering Corp. | Stereotaxic catheter for microwave thermotherapy |
US4735201A (en) | 1986-01-30 | 1988-04-05 | The Beth Israel Hospital Association | Optical fiber with detachable metallic tip for intravascular laser coagulation of arteries, veins, aneurysms, vascular malformations and arteriovenous fistulas |
US5002548A (en) | 1986-10-06 | 1991-03-26 | Bio Medic Data Systems, Inc. | Animal marker implanting system |
US4787384A (en) | 1986-10-06 | 1988-11-29 | Bio Medic Data System, Inc. | Animal marker implanting system |
US4931059A (en) | 1986-11-24 | 1990-06-05 | Markham Charles W | Needle/stylet combination |
US4774948A (en) | 1986-11-24 | 1988-10-04 | Markham Charles W | Marking and retraction needle having retrievable stylet |
US4819630A (en) | 1987-03-20 | 1989-04-11 | Laser Photonics, Inc. | Flexible light transmissive apparatus and method |
US4957481A (en) | 1987-10-01 | 1990-09-18 | U.S. Bioscience | Photodynamic therapeutic technique |
US4991579A (en) * | 1987-11-10 | 1991-02-12 | Allen George S | Method and apparatus for providing related images over time of a portion of the anatomy using fiducial implants |
JPH01139081A (en) | 1987-11-27 | 1989-05-31 | Olympus Optical Co Ltd | Apparatus for radiating laser beam |
JPH01148280A (en) * | 1987-12-05 | 1989-06-09 | Olympus Optical Co Ltd | Laser irradiator |
US5195526A (en) | 1988-03-11 | 1993-03-23 | Michelson Gary K | Spinal marker needle |
US4883062A (en) | 1988-04-25 | 1989-11-28 | Medex, Inc. | Temperture and pressure monitors utilizing interference filters |
US4959063A (en) | 1988-05-12 | 1990-09-25 | Osada Research Institute, Ltd. | Spinal needle with optical fiber means for radiating a laser beam |
US5242437A (en) | 1988-06-10 | 1993-09-07 | Trimedyne Laser Systems, Inc. | Medical device applying localized high intensity light and heat, particularly for destruction of the endometrium |
US4967765A (en) | 1988-07-28 | 1990-11-06 | Bsd Medical Corporation | Urethral inserted applicator for prostate hyperthermia |
US5125925A (en) | 1988-08-03 | 1992-06-30 | Photoradiation Systems | Intracavity laser catheter with sensing fiber |
US4890898A (en) | 1988-08-18 | 1990-01-02 | Hgm Medical Laser Systems, Inc. | Composite microsize optical fiber-electric lead cable |
US4920978A (en) | 1988-08-31 | 1990-05-01 | Triangle Research And Development Corporation | Method and apparatus for the endoscopic treatment of deep tumors using RF hyperthermia |
US4946440A (en) | 1988-10-05 | 1990-08-07 | Hall John E | Evertible membrane catheter and method of use |
IL89874A0 (en) * | 1989-04-06 | 1989-12-15 | Nissim Nejat Danon | Apparatus for computerized laser surgery |
GB2230191B (en) | 1989-04-15 | 1992-04-22 | Robert Graham Urie | Lesion location device |
US5234426A (en) | 1989-06-15 | 1993-08-10 | Research Corporation Technologies, Inc. | Helical-tipped lesion localization needle device and method of using the same |
US5061265A (en) | 1989-06-20 | 1991-10-29 | University Of Florida | Laser treatment apparatus and method |
US5129896A (en) | 1989-11-13 | 1992-07-14 | Hasson Harrith M | Holder to facilitate use of a laser in surgical procedures |
US5240011A (en) | 1991-11-27 | 1993-08-31 | Fischer Imaging Corporation | Motorized biopsy needle positioner |
US5078142A (en) | 1989-11-21 | 1992-01-07 | Fischer Imaging Corporation | Precision mammographic needle biopsy system |
US5415169A (en) | 1989-11-21 | 1995-05-16 | Fischer Imaging Corporation | Motorized mammographic biopsy apparatus |
US5158084A (en) | 1989-11-22 | 1992-10-27 | Board Of Regents, The University Of Texas System | Modified localization wire for excisional biopsy |
US5201729A (en) | 1990-01-12 | 1993-04-13 | Laserscope | Method for performing percutaneous diskectomy using a laser |
US5116345A (en) * | 1990-11-28 | 1992-05-26 | Ohio Medical Instrument Co., Inc. | Stereotactically implanting an intracranial device |
US5127916A (en) | 1991-01-22 | 1992-07-07 | Medical Device Technologies, Inc. | Localization needle assembly |
FR2675371A1 (en) | 1991-04-22 | 1992-10-23 | Technomed Int Sa | DEVICE FOR THERMAL TREATMENT OF FABRICS BY PULSE SEQUENCE GROUP. |
US5301671A (en) * | 1991-09-17 | 1994-04-12 | The United States Of America As Represented By The Department Of Health And Human Services | Two- and three-dimensional autoradiographic imaging utilizing charge coupled devices |
US5222953A (en) | 1991-10-02 | 1993-06-29 | Kambiz Dowlatshahi | Apparatus for interstitial laser therapy having an improved temperature sensor for tissue being treated |
US5681282A (en) | 1992-01-07 | 1997-10-28 | Arthrocare Corporation | Methods and apparatus for ablation of luminal tissues |
WO1993014694A1 (en) | 1992-01-16 | 1993-08-05 | The General Hospital Corporation | Method and apparatus for locating tumors |
MX9300607A (en) | 1992-02-06 | 1993-10-01 | American Med Syst | APPARATUS AND METHOD FOR INTERSTITIAL TREATMENT. |
US5484400A (en) | 1992-08-12 | 1996-01-16 | Vidamed, Inc. | Dual channel RF delivery system |
US5486161A (en) | 1993-02-02 | 1996-01-23 | Zomed International | Medical probe device and method |
US5312392A (en) | 1992-08-31 | 1994-05-17 | Messerschmitt-Boelkow-Blohm Ag | Interstitial laser coagulation treatment for benign prostatic hyperplasia |
US5386447A (en) | 1992-09-23 | 1995-01-31 | Fischer Imaging Corporation | Mammographic screening and biopsy apparatus |
TW259716B (en) | 1992-10-09 | 1995-10-11 | Birtcher Med Syst | |
USD344903S (en) | 1992-11-25 | 1994-03-08 | Surgical Technologies, Inc. | Bipolar probe |
US5575794A (en) | 1993-02-12 | 1996-11-19 | Walus; Richard L. | Tool for implanting a fiducial marker |
US5307812A (en) * | 1993-03-26 | 1994-05-03 | General Electric Company | Heat surgery system monitored by real-time magnetic resonance profiling |
US5472441A (en) | 1993-11-08 | 1995-12-05 | Zomed International | Device for treating cancer and non-malignant tumors and methods |
US6071280A (en) | 1993-11-08 | 2000-06-06 | Rita Medical Systems, Inc. | Multiple electrode ablation apparatus |
US5599346A (en) | 1993-11-08 | 1997-02-04 | Zomed International, Inc. | RF treatment system |
US5728143A (en) | 1995-08-15 | 1998-03-17 | Rita Medical Systems, Inc. | Multiple antenna ablation apparatus and method |
US5683384A (en) | 1993-11-08 | 1997-11-04 | Zomed | Multiple antenna ablation apparatus |
US5458597A (en) | 1993-11-08 | 1995-10-17 | Zomed International | Device for treating cancer and non-malignant tumors and methods |
US5536267A (en) | 1993-11-08 | 1996-07-16 | Zomed International | Multiple electrode ablation apparatus |
US5928229A (en) | 1993-11-08 | 1999-07-27 | Rita Medical Systems, Inc. | Tumor ablation apparatus |
US6241725B1 (en) * | 1993-12-15 | 2001-06-05 | Sherwood Services Ag | High frequency thermal ablation of cancerous tumors and functional targets with image data assistance |
US5954711A (en) | 1993-12-28 | 1999-09-21 | Nidek Co., Ltd. | Laser treatment apparatus |
US5615430A (en) | 1994-08-22 | 1997-04-01 | Kabushiki Kaisha Toshiba | Medical bed system |
US6106524A (en) | 1995-03-03 | 2000-08-22 | Neothermia Corporation | Methods and apparatus for therapeutic cauterization of predetermined volumes of biological tissue |
US5813985A (en) * | 1995-07-31 | 1998-09-29 | Care Wise Medical Products Corporation | Apparatus and methods for providing attenuation guidance and tumor targeting for external beam radiation therapy administration |
US5863290A (en) | 1995-08-15 | 1999-01-26 | Rita Medical Systems | Multiple antenna ablation apparatus and method |
US5782827A (en) | 1995-08-15 | 1998-07-21 | Rita Medical Systems, Inc. | Multiple antenna ablation apparatus and method with multiple sensor feedback |
US5913855A (en) | 1995-08-15 | 1999-06-22 | Rita Medical Systems, Inc. | Multiple antenna ablation apparatus and method |
US5980517A (en) | 1995-08-15 | 1999-11-09 | Rita Medical Systems, Inc. | Cell necrosis apparatus |
US6235023B1 (en) * | 1995-08-15 | 2001-05-22 | Rita Medical Systems, Inc. | Cell necrosis apparatus |
US5672173A (en) | 1995-08-15 | 1997-09-30 | Rita Medical Systems, Inc. | Multiple antenna ablation apparatus and method |
US5672174A (en) | 1995-08-15 | 1997-09-30 | Rita Medical Systems, Inc. | Multiple antenna ablation apparatus and method |
SE505513C2 (en) | 1995-11-14 | 1997-09-08 | Elekta Ab | Device for repositioning a patient |
US5636255A (en) | 1996-03-05 | 1997-06-03 | Queen's University At Kingston | Method and apparatus for CT image registration |
US5853366A (en) | 1996-07-08 | 1998-12-29 | Kelsey, Inc. | Marker element for interstitial treatment and localizing device and method using same |
US6023637A (en) * | 1997-03-31 | 2000-02-08 | Liu; Zhong Qi | Method and apparatus for thermal radiation imaging |
ES2353846T3 (en) * | 1997-04-11 | 2011-03-07 | United States Surgical Corporation | APPLIANCE FOR RF ABLATION AND CONTROLLER OF THE SAME. |
US6058322A (en) | 1997-07-25 | 2000-05-02 | Arch Development Corporation | Methods for improving the accuracy in differential diagnosis on radiologic examinations |
US6094760A (en) | 1997-08-04 | 2000-08-01 | Sumitomo Heavy Industries, Ltd. | Bed system for radiation therapy |
JPH11221229A (en) | 1997-09-24 | 1999-08-17 | Eclipse Surgical Technol Inc | Catheter |
US6517534B1 (en) * | 1998-02-11 | 2003-02-11 | Cosman Company, Inc. | Peri-urethral ablation |
US6131579A (en) | 1998-04-21 | 2000-10-17 | Somnus Medical Technologies, Inc. | Wire based temperature sensing electrode |
US6341893B1 (en) | 1998-07-23 | 2002-01-29 | Canon Kabushiki Kaisha | Photographing stand with a radiation image receiving portion |
JP3204310B2 (en) | 1998-08-12 | 2001-09-04 | 日本電気株式会社 | CDMA mobile communication system and downlink transmission power control method thereof |
US6451015B1 (en) * | 1998-11-18 | 2002-09-17 | Sherwood Services Ag | Method and system for menu-driven two-dimensional display lesion generator |
JP2000237205A (en) * | 1999-02-17 | 2000-09-05 | Toshiba Corp | Ultrasonic therapeutic apparatus |
US6456684B1 (en) | 1999-07-23 | 2002-09-24 | Inki Mun | Surgical scanning system and process for use thereof |
US6498942B1 (en) * | 1999-08-06 | 2002-12-24 | The University Of Texas System | Optoacoustic monitoring of blood oxygenation |
US6254614B1 (en) | 1999-10-18 | 2001-07-03 | Jerry M. Jesseph | Device and method for improved diagnosis and treatment of cancer |
US7615076B2 (en) | 1999-10-20 | 2009-11-10 | Anulex Technologies, Inc. | Method and apparatus for the treatment of the intervertebral disc annulus |
US6542767B1 (en) | 1999-11-09 | 2003-04-01 | Biotex, Inc. | Method and system for controlling heat delivery to a target |
WO2001074251A2 (en) * | 2000-03-31 | 2001-10-11 | Rita Medical Systems Inc. | Tissue biopsy and treatment apparatus and method |
US6470217B1 (en) | 2000-04-13 | 2002-10-22 | Celsion Corporation | Method for heating ductal and glandular carcinomas and other breast lesions to perform thermal downsizing and a thermal lumpectomy |
JP4503229B2 (en) | 2000-06-20 | 2010-07-14 | ボストン・サイエンティフィック・コーポレーション | System and method for heating the prostate using microwaves |
DE60043788D1 (en) | 2000-11-17 | 2010-03-18 | Calypso Medical Inc | SYSTEM FOR LOCALIZING AND DEFINING A TARGET POSITION IN A HUMAN BODY |
DE10127210B4 (en) | 2001-06-05 | 2004-09-23 | Deutsches Krebsforschungszentrum Stiftung des öffentlichen Rechts | Patient positioning and transportation system |
US20030035868A1 (en) | 2001-08-15 | 2003-02-20 | Packaging Specialties, Inc. | Method for producing food product packages with modified environment packaging |
US20030060813A1 (en) | 2001-09-22 | 2003-03-27 | Loeb Marvin P. | Devices and methods for safely shrinking tissues surrounding a duct, hollow organ or body cavity |
US7399300B2 (en) | 2001-12-04 | 2008-07-15 | Endoscopic Technologies, Inc. | Cardiac ablation devices and methods |
US7041109B2 (en) | 2002-12-12 | 2006-05-09 | Kelsey, Inc. | Apparatus and method for interstitial laser therapy of small breast cancers and adjunctive therapy |
US20050113641A1 (en) | 2003-11-22 | 2005-05-26 | Bala John L. | Endoscopic imaging and intervention system |
US20060095096A1 (en) | 2004-09-09 | 2006-05-04 | Debenedictis Leonard C | Interchangeable tips for medical laser treatments and methods for using same |
-
2001
- 2001-04-13 US US09/834,873 patent/US6603988B2/en not_active Expired - Lifetime
-
2002
- 2002-04-12 BR BRPI0208877-0A patent/BR0208877B1/en not_active IP Right Cessation
- 2002-04-12 RU RU2003133134/14A patent/RU2003133134A/en not_active Application Discontinuation
- 2002-04-12 CN CNB028105494A patent/CN1263422C/en not_active Expired - Lifetime
- 2002-04-12 NZ NZ529478A patent/NZ529478A/en not_active IP Right Cessation
- 2002-04-12 DE DE20221877U patent/DE20221877U1/en not_active Expired - Lifetime
- 2002-04-12 WO PCT/US2002/011452 patent/WO2002082993A1/en active IP Right Grant
- 2002-04-12 JP JP2002580802A patent/JP4338976B2/en not_active Expired - Lifetime
- 2002-04-12 AU AU2002303314A patent/AU2002303314B2/en not_active Expired
- 2002-04-12 ES ES02731333T patent/ES2290301T3/en not_active Expired - Lifetime
- 2002-04-12 EP EP02731333A patent/EP1377210B1/en not_active Expired - Lifetime
- 2002-04-12 AT AT02731333T patent/ATE367774T1/en active
- 2002-04-12 DE DE60221371T patent/DE60221371T2/en not_active Expired - Lifetime
- 2002-04-12 MX MXPA03009295A patent/MXPA03009295A/en active IP Right Grant
- 2002-04-12 CA CA2443739A patent/CA2443739C/en not_active Expired - Lifetime
- 2002-10-03 US US10/263,639 patent/US6701175B2/en not_active Expired - Lifetime
-
2003
- 2003-10-14 ZA ZA200307987A patent/ZA200307987B/en unknown
-
2004
- 2004-01-09 US US10/754,827 patent/US6865412B2/en not_active Expired - Lifetime
-
2005
- 2005-02-14 US US11/057,916 patent/US7171253B2/en not_active Expired - Lifetime
-
2006
- 2006-12-20 US US11/643,515 patent/US7725155B2/en not_active Expired - Fee Related
-
2008
- 2008-06-20 AT AT0035108U patent/AT11291U1/en not_active IP Right Cessation
-
2010
- 2010-04-16 US US12/761,760 patent/US10765342B2/en active Active
Patent Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5178148A (en) * | 1990-04-06 | 1993-01-12 | Technomed International | Method of automatically measuring the volume of a tumor or of a gland, in particular the prostate, a measuring device, and a method and apparatus constituting and application thereof |
US5569240A (en) * | 1990-06-08 | 1996-10-29 | Kelsey, Inc. | Apparatus for interstitial laser therapy |
US5620479A (en) * | 1992-11-13 | 1997-04-15 | The Regents Of The University Of California | Method and apparatus for thermal therapy of tumors |
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