ABLATION PROBE SYSTEMS.

Abstract

An ablation probe tip (100) having a shaft (102) with an insertion end (104) and an annular opening (120) near the insertion end (104). An ablation center (124) is located within the shaft (102) and surrounded by the annular opening of the shaft (102). The ablation probe tip (100) may be part of an ablation probe system (50) that includes an ablation source (60) that provides ablation media (62) to the ablation probe tip (100). The ablation center (124) is a focal region from which the ablation media (62) radiates through the annular opening (120) to form an ablation zone (150, 160, 170). The system (50) has at least one intraoperative control selected from the group of: ablation zone positioning control, ablation zone shaping control, ablation center control, ablation zone temperature control, and guided ablation volume / diameter control.

Description

This disclosure describes devices, methods / procedures, and systems that generally pertain to the technical field of ablation probes, and specifically to the technical field of microwave and radiofrequency ablation probes that have target tissue ablation zones shaped and / or sized to enable guided soft tissue ablation procedures that are more accurate and predictable than unguided procedures. The term ablation in the medical industry generally describes the removal of problematic (e.g., damaged, diseased, or unwanted) tissue (target tissue) using less invasive techniques. These techniques typically employ a probe that operates by cooling or heating the target tissue, although mechanical, electrical, chemical, and laser ablation technologies can also be used. While resection involves the partial or total removal of an organ using conventional surgical methods (i.e., using a scalpel or saw to cut the tissue), medical ablation generally involves the partial or total removal or destruction of a layer (or layers) of the target tissue using a probe that employs thermal or non-thermal technology. The goal is to restore normal function by more selectively destroying the target tissue.The goal of ablation is to remove or destroy the target tissue (the problematic tissue) with substantially less damage to surrounding tissue or structure compared to more invasive, conventional surgical methods. Ablation technology can be used to treat a range of conditions, from serious to cosmetic.Some of the most common types of ablation are surface ablation (used to remove a layer of target tissue to treat discoloration, improve skin texture, or remove superficial lesions, warts, or tumors), cardiac ablation (such as radiofrequency ablation (RFA), which is used to destroy target tissue in the heart associated with irregular heartbeats), microwave endometrial ablation (used to destroy the lining of the uterus in order to reduce or stop abnormal bleeding from the uterus), bone marrow ablation (used to remove bone marrow before a bone marrow transplant), and ablative brain surgery (used to treat certain neurological disorders) or microwave ablation (used to treat liver tumors without physically removing them). Ablation can be performed using microwaves (e.g., microwave ablation (MA) and microwave endometrial ablation (MEA)), radiofrequency (e.g., radiofrequency ablation (RFA)), lasers (e.g., LASIK surgery), ultrasound (e.g., ultra-high-intensity ultrasound), chemicals (e.g., chemoablation), low or cold temperatures (e.g., cryoablation), high or hot temperatures, electricity (e.g., fulguration, hot point or cauterization, and others), and mechanical processes (e.g., rotablation). Microwave ablation is a form of thermal ablation that uses electromagnetic waves in the microwave energy spectrum (300 MHz to 300 GHz) to produce tissue heating effects in order to induce tissue necrosis within solid tumors to treat cancer.Microwave endometrial ablation, for example, is a use of microwave ablation that employs microwaves at a fixed frequency to destroy the basal layer of the endometrium and glands (preserving the rest of the uterus) by heating them to over 60°C. Another well-established use of microwave ablation is the ablation of liver tumors, which is typically performed at a frequency of 500 MHz to 2.45 GHz. Radiofrequency ablation (RFA) is a medical procedure in which part of the heart's electrical conduction system, a tumor, or other dysfunctional tissue is ablated using heat generated by medium-frequency alternating current (in the 300–500 kHz range). One of the uses of ablation is the removal of tooth buds. The formation of third molars predictably causes lifelong problems, such as complications, pain, cavities, gum disease, and / or abscesses, with a rate of nearly 99% over the lifetime of patients. Unfortunately, the surgical extraction of fully formed third molars carries a number of risks and complications, including painful post-extraction osteitis or dry socket, serious infections, temporary and permanent nerve damage, significant pain, temporary and permanent damage to the temporomandibular joint (TMJ), etc. Historically, there have been suggestions and attempts to prevent the formation of third molars prophylactically before these problematic teeth fully develop, such as those of Dr. Henry in 1969, Drs. Gordon and Laskin in 1978, and, more recently, Dr.Silvestri proposed in 2004 that these methods aim to eliminate the conditions that predictably cause the disease, while simultaneously eliminating surgical risks. However, these manual systems have proven difficult to implement, inconsistent, unpredictable, and unrepeatable due to their manual nature, and as a result, they have never been widely adopted by dentists. Illustrative guided ablation systems and methods for the ablation of dental outlines, as described in U.S. Patent No. 9,402,693, U.S. Patent No. 9,827,068, U.S. Patent No. 9,855,112, U.S. Patent No. 10,022,202, U.S. Patent No. 10,265,140, ​​U.S. Patent No. 10,285,778 and U.S. Patent No. 10,298,255, U.S. Patent No. 10,299,885, U.S. Patent Publication No. US2011 / 0200961, U.S. Patent Publication No. US2016 / 0324597, publication ML / IZ / ZZZZ / UII and U.S. Patent No. US2017 / 0360528, U.S. Patent Publication No. US2018 / 0091169, U.S. Patent Publication No. US2018 / 0153640, U.S. Patent Publication No. US2018 / 0318038, PCT Publication No. WO / 2010 / 132368, PCT Publication No. WO / 2014 / 143014, and related U.S. and foreign patent applications, all of which were invented by the inventor of the present invention and are owned by the applicant of the present application. Disclosures of these references, hereinafter referred to as Dental Outline Ablation Therapeutic Properties, are expressly incorporated herein by reference. The therapeutic properties of dental bud ablation describe methods, systems, and procedures for ablating dental buds that result in dental agenesis.These methods, systems, and procedures may include and / or utilize ablation probe tips and / or stents. The NEUWAVE™ microwave ablation system is described as capable of ablating lesions with consistency and control to help protect non-target tissue. The NEUWAVE™ system includes features such as a computer-controlled system for storing procedure data and ablation confirmation software to verify the technical success of procedures. It is described as having a burn pattern that controls the ablation distance beyond the probe tip, limiting the burn pattern beyond the tip. Although NEUWAVE claims that the PR probe is the only probe available with a unique burn pattern that controls the ablation distance beyond the probe tip, the NEUWAVE microwave ablation PR probe has serious limitations. The ablation produced by the PR probe covers the tip in 10 seconds and then burns proximally.This means that the burn pattern creeps or migrates asymmetrically (which will be generically referred to as migrations or variations thereof) upwards from the tip of the ablation probe (generally away from the absolute tip and towards a handle) with a resulting burn pattern that is so oblong that it is shaped like a "hot dog," making minimally invasive soft tissue ablation procedures impossible. Migration of the ablation zone above the probe tip (generally away from the absolute tip and toward a handle) is a well-known problem throughout the ablation medical community, and numerous attempts have been made to control it. For example, U.S. Patent No. 7,611,508 to Yang et al. establishes an antenna for microwave ablation of tumors having coaxial antenna conductors surrounded by an insulated sheath of a length and size that promotes destructive interference of axial microwave energy passing inside and outside the sheath to limit the tailing (which, as it trails, will also be generically referred to as migration or variations thereof) of the burn pattern upward from the axis of the microwave ablation probe tip. The sheath ML / IZ / ZZZZ / υUII and Yang's floating UII provides destructive wave interference or cancellation of the microwave signal radiating from the antennas, but this documentation shows that this technique still results in an ablation zone that migrates asymmetrically upwards along the length of the probe during soft tissue ablation with a pattern so oblong that it resembles a "hot dog," making minimally invasive soft tissue ablation procedures impossible. BRIEF DESCRIPTION This disclosure describes devices, methods / procedures, and systems that generally pertain to the technical field of medical ablation probes, and specifically to the technical field of microwave ablation probes and radiofrequency ablation probes that provide target tissue ablation zones of shape and / or size, along with the ability to eliminate migration of the ablation zone (the burn pattern) upward from the probe tip axis through a stationary ablation center, while simultaneously controlling the power load (power density) on the tissue to maximize or minimize the peak temperatures in the active heating zone in the ablation target tissue. A first preferred ablation probe tip preferably has a shaft with an insertion end. The ablation probe tip preferably receives ablation media from an ablation source. The ablation probe tip preferably serves for the ablation of the target tissue. The ablation probe tip preferably includes: the shaft, an annular aperture, and an ablation center. The shaft preferably includes a coaxial antenna. The annular aperture is preferably defined in at least one outer layer of the coaxial antenna toward the insertion end. The ablation center is preferably located within the coaxial antenna and is surrounded by the annular aperture. The ablation center can be considered a focal region from which the ablation media radiates through the annular aperture to form an ablation zone. The ablation zone preferably has a predetermined power charge density. In an alternative to the first tip of the preferred ablation probe, the ablation zone selectively ablates the target tissue while mitigating damage to immediately adjacent collateral tissues. In an alternative to the first tip of the preferred ablation probe, the ablation zone destroys at least part of the target tissue. In an alternative to the first preferred ablation probe tip, the annular aperture is preferably a short annular aperture that preferably creates a short active heating zone surrounding the annular aperture. The short active heating zone preferably creates a high power load in the ablation zone. The short active heating zone preferably creates high peak temperatures in the ablation zone. In an alternative to the first preferred ablation probe tip, the annular aperture is preferably a mid-annular aperture that preferably creates a mid-active heating zone surrounding the annular aperture. The mid-active heating zone preferably creates a mid-power load in the ablation zone. The mid-active heating zone preferably creates mid-peak temperatures in the ablation zone. In an alternative to the first preferred ablation probe tip, the annular aperture is preferably a long annular aperture that preferably creates a long active heating zone surrounding the annular aperture. The long active heating zone preferably creates a low power load in the ablation zone. The long active heating zone preferably creates low peak temperatures in the ablation zone. In an alternative to the first preferred ablation probe tip, the coaxial antenna is preferably a near-field antenna. The ablation center is preferably a stationary ablation center. The near-field antenna preferably prevents the ablation center from migrating up the axis away from the insertion end. An alternative to the first preferred ablation probe tip further includes an annular heat transfer layer surrounding the coaxial antenna. The annular heat transfer layer may surround the coaxial antenna and be separated from the insertion end such that the annular aperture is located between the annular heat transfer layer and the insertion end. The annular heat transfer layer preferably prevents the ablation center from migrating upward along the axis away from the insertion end. In an alternative to the first preferred ablation probe tip, the ablation zone preferably has a predetermined shape selected from the group consisting of oblate, spherical, and oblong. An alternative to the first tip of the preferred ablation probe further includes an annular heat transfer layer surrounding the coaxial antenna and separated from the insertion end, such that the annular aperture is located between the annular heat transfer layer and the insertion end. The ablation zone preferably has a predetermined shape determined by an aperture offset. The aperture offset is preferably a distance between the ablation center and an annular edge of the annular heat transfer layer. An oblong ablation zone preferably has a relatively short aperture offset. A spherical ablation zone preferably has an aperture offset between the aperture offsets of the oblong and oblong ablation zones. An alternative to the first preferred ablation probe tip further includes an annular heat transfer layer surrounding the coaxial antenna. The coaxial antenna further includes an annular insulating layer surrounding the coaxial antenna. The annular heat transfer layer preferably surrounds the annular insulating layer. In an alternative to the first preferred ablation probe tip, an antenna end load is preferably placed between the annular aperture and the insertion end. The antenna end load can concentrate the energy density and increase the power load. An alternative to the first preferred ablation probe tip further includes an annular heat transfer layer surrounding the coaxial antenna and separated from the insertion end, such that the annular aperture is between the annular heat transfer layer and the insertion end. The annular heat transfer layer preferably has high thermal conductivity and is preferably electrically conductive. In an alternative to the first preferred ablation probe tip, the coaxial antenna includes an inner conductor, an annular dielectric insulating layer surrounding the inner conductor, and an outer annular conductor surrounding the annular dielectric insulating layer. The annular aperture exposes an annular ring of the annular dielectric insulating layer. In an alternative to the first preferred ablation probe tip, the ablation probe tip is preferably part of a surgical ablation kit that includes an ablation source, a handpiece, a stent, and a prescription. The prescription preferably includes at least one setting or parameter selected from the group consisting of: ablation energy dose tolerances, energy levels, and energy delivery duration. In an alternative to the first preferred ablation probe tip, the ablation probe tip is preferably used in conjunction with a stent. The stent preferably has a surgical guide. The surgical guide preferably serves to guide the ablation probe tip so that the ablation center is within the tissue. As an alternative to the first preferred ablation probe tip, the coaxial antenna is preferably a near-field reactive antenna. An alternative to the first tip of the preferred ablation probe further includes an annular heat transfer layer surrounding the coaxial antenna and separated from the insertion end, such that the annular aperture is between the annular heat transfer layer and the insertion end. Preferably, the annular heat transfer layer prevents the ablation media from migrating upward along the shaft, away from the insertion end. Preferably, the annular heat transfer layer allows thermal energy from the ablation zone to travel upward along the shaft, away from the insertion end. In an alternative to the first preferred ablation probe tip, the ablation probe tip is preferably part of an ablation probe system that preferably has intraoperative control of the selected maximum temperature group consisting of: passive cooling, active cooling, and a combination of passive and active cooling. An alternative to the first preferred ablation probe tip further includes an annular heat transfer layer surrounding the coaxial antenna and separated from the insertion end, such that the annular aperture is located between the annular heat transfer layer and the insertion end. The annular heat transfer layer is preferably quenched by the transfer of thermal energy from the annular heat transfer layer to the soft tissue surrounding the annular heat transfer layer. In an alternative to the first preferred ablation probe tip, the ablation probe tip is preferably part of an ablation probe system that preferably has intraoperative control of the ablation zone volume. In an alternative to the first preferred ablation probe tip, the ablation probe tip is preferably part of an ablation probe system that preferably has intraoperative control of the ablation zone diameter. In an alternative to the first preferred ablation probe tip, the ablation probe tip and the ablation media together allow at least one selected intraoperative control of the group consisting of: ablation zone position, ablation zone shape, ablation zone centering, maximum ablation zone temperature, ablation zone volume, and ablation zone diameter. As an alternative to the first preferred ablation probe tip, the ablation probe tip is preferably a microablation probe tip. As an alternative to the first preferred ablation probe tip, the ablation probe tip is preferably a microwave ablation probe tip. The microwave ablation probe tip can receive microwave energy from the ablation source as the ablation medium. The microwave energy can be delivered to the target tissue through the ablation probe tip. The ablation source can provide microwave energy at frequencies ranging from 500 MHz to 20 GHz. As an alternative to the first preferred ablation probe tip, the ivia / t / zuzz / ui ui iy ablation probe tip is preferably a radiofrequency ablation probe tip. A second preferred ablation probe tip preferably has a shaft with an insertion end. The ablation probe tip preferably receives ablation media from an ablation source. The ablation probe tip preferably serves for the ablation of the target tissue. The ablation probe tip preferably includes: the shaft, an annular aperture, and an ablation center. The shaft preferably includes a coaxial antenna. The annular aperture is preferably defined in at least one outer layer of the coaxial antenna toward the insertion end. The ablation center is preferably located within the coaxial antenna and surrounded by the annular aperture. The ablation center can be considered a focal region from which the ablation media radiate through the annular aperture to form an ablation zone. The ablation zone preferably has a predetermined maximum temperature. In an alternative to the second tip of the preferred ablation probe, the ablation zone selectively ablates the target tissue while mitigating damage to immediately adjacent collateral tissues. In another alternative to the second tip of the preferred ablation probe, the ablation zone destroys at least part of the target tissue. In an alternative to the second preferred ablation probe tip, the annular aperture is preferably a short annular aperture that preferably creates a short active heating zone surrounding the annular aperture. The short active heating zone preferably creates a high power load in the ablation zone. The short active heating zone preferably creates high peak temperatures in the ablation zone. In an alternative to the second preferred ablation probe tip, the annular aperture is preferably a mid-annular aperture that preferably creates a mid-active heating zone surrounding the annular aperture. The mid-active heating zone preferably creates a mid-power load in the ablation zone. The mid-active heating zone preferably creates mid-peak temperatures in the ablation zone. In an alternative to the second preferred ablation probe tip, the annular aperture is preferably a long annular aperture that preferably creates a long active heating zone surrounding the annular aperture. The long active heating zone preferably creates a low power load in the ablation zone. The long active heating zone preferably creates low peak temperatures in the ablation zone. In an alternative to the second preferred ablation probe tip, the coaxial antenna is preferably a near-field antenna. The ablation center is preferably a stationary ablation center. The near-field antenna preferably prevents the ablation center from migrating up the axis away from the insertion end. An alternative to the second preferred ablation probe tip further includes an annular heat transfer layer surrounding the coaxial antenna. The annular heat transfer layer may surround the coaxial antenna and be separated from the insertion end such that the annular aperture is located between the annular heat transfer layer and the insertion end. The annular heat transfer layer preferably prevents the ablation center from migrating upward along the axis away from the insertion end. In an alternative to the second tip of the preferred ablation probe, the ablation zone preferably has a predetermined shape selected from the group consisting of oblate, spherical, and oblong. An alternative for the second tip of the preferred ablation probe further includes an annular heat transfer layer surrounding the coaxial antenna and spaced from the insertion end, such that the annular aperture is between the annular heat transfer layer and the insertion end. The ablation zone preferably has a predetermined shape determined by an aperture offset. The aperture offset is preferably a distance between the ablation center and an annular edge of the annular heat transfer layer. An oblate ablation zone preferably has a relatively short aperture offset. An oblong ablation zone preferably has a relatively long aperture offset. A spherical ablation zone preferably has an aperture offset between the aperture offsets of the oblate and oblong ablation zones. An alternative to the second preferred ablation probe tip further includes an annular heat transfer layer surrounding the coaxial antenna. The coaxial antenna further includes an annular insulating layer surrounding the coaxial antenna. The annular heat transfer layer preferably surrounds the annular insulating layer. In an alternative to the second preferred ablation probe tip, an antenna end load is preferably placed between the annular aperture and the insertion end. The antenna end load can concentrate the energy density and increase the power load. An alternative to the second preferred ablation probe tip further includes an annular heat transfer layer surrounding the coaxial antenna and separated from the insertion end, such that the annular aperture is between the annular heat transfer layer and the insertion end. The annular heat transfer layer preferably has high thermal conductivity and is preferably electrically conductive. In an alternative to the second preferred ablation probe tip, the coaxial antenna includes an inner conductor, an annular dielectric insulating layer surrounding the inner conductor, and an outer annular conductor surrounding the annular dielectric insulating layer. The annular aperture exposes an annular ring of the annular dielectric insulating layer. In an alternative to the second preferred ablation probe tip, the ablation probe tip is preferably part of a surgical ablation kit that includes an ablation source, a handpiece, a stent, and a prescription. The prescription preferably includes at least one setting or parameter selected from the group consisting of: ablation energy dose tolerances, energy levels, and energy delivery duration. In an alternative to the preferred second ablation probe tip, the ablation probe tip is preferably used in conjunction with a stent. The stent preferably has a surgical guide. The surgical guide preferably serves to guide the ablation probe tip so that the ablation center is within the tissue. As an alternative to the second preferred ablation probe tip, the coaxial antenna is preferably a near-field reactive antenna. An alternative for the second tip of the preferred ablation probe further includes an annular heat transfer layer surrounding the coaxial antenna and separated from the insertion end, such that the annular aperture is between the annular heat transfer layer and the insertion end. Preferably, the annular heat transfer layer prevents the ablation media from migrating upward along the shaft, away from the insertion end. Alternatively, the annular heat transfer layer may allow thermal energy from the ablation zone to travel upward along the shaft, away from the insertion end. In an alternative to the second preferred ablation probe tip, the ablation probe tip is preferably part of an ablation probe system that preferably has intraoperative maximum temperature control selected from the group consisting of: passive cooling, active cooling, and a combination of passive and active cooling. An alternative to the second preferred ablation probe tip further includes an annular heat transfer layer surrounding the coaxial antenna and separated from the insertion end, such that the annular aperture is located between the annular heat transfer layer and the insertion end. The annular heat transfer layer is preferably quenched by the transfer of thermal energy from the annular heat transfer layer to the soft tissue surrounding the annular heat transfer layer. ML / E / ZuZz / u UI 1 In an alternative to the second preferred ablation probe tip, the ablation probe tip is preferably part of an ablation probe system that preferably has intraoperative control of the ablation zone volume. In an alternative to the second preferred ablation probe tip, the ablation probe tip is preferably part of an ablation probe system that preferably has intraoperative control of the ablation zone diameter. In an alternative to the second preferred ablation probe tip, the ablation probe tip and the ablation media together allow at least one selected intraoperative control of the group consisting of: ablation zone position, ablation zone shape, ablation zone centering, maximum ablation zone temperature, ablation zone volume, and ablation zone diameter. As an alternative to the second preferred ablation probe tip, the ablation probe tip is preferably a microablation probe tip. As an alternative to the second preferred ablation probe tip, the ablation probe tip is preferably a microwave ablation probe tip. The microwave ablation probe tip can receive microwave energy from the ablation source as the ablation medium. The microwave energy can be delivered to the target tissue through the ablation probe tip. The ablation source can provide microwave energy at frequencies ranging from 500 MHz to 20 GHz. As an alternative to the second preferred ablation probe tip, the ablation probe tip is preferably a radiofrequency ablation probe tip. A third preferred ablation probe tip preferably has a shaft with an insertion end. The ablation probe tip preferably receives ablation media from an ablation source. The ablation probe tip preferably serves for ablation of the target tissue. The ablation probe tip preferably includes: the shaft, an annular aperture, and an ablation center. The shaft preferably includes a coaxial antenna. The annular aperture is preferably defined in at least one outer layer of the coaxial antenna toward the insertion end. The ablation center is preferably located within the coaxial antenna and surrounded by the annular aperture. The ablation center can be considered a focal region from which the ablation media radiate through the annular aperture to form an ablation zone.The ablation zone preferably has an annular aperture and a power load density in the ablation zone, the annular aperture and power load density being selected from the group consisting of: (a) a short annular aperture and a high power load; (b) a medium annular aperture and a medium power load; and (c) a long annular aperture and a low power load. In an alternative to the preferred third ablation probe tip, the ablation zone selectively ablates the target tissue while mitigating damage to immediately adjacent collateral tissues. In another alternative to the preferred third ablation probe tip, the ablation zone destroys at least part of the target tissue. In an alternative to the third preferred ablation probe tip, the ablation zone preferably has a peak temperature in the selected ablation zone from the group consisting of: (a) if the annular aperture is a short annular aperture, the peak temperature in the ablation zone is a high peak temperature; (b) if the annular aperture is a medium annular aperture, the peak temperature in the ablation zone is a medium peak temperature; and (c) if the annular aperture is a long annular aperture, the peak temperature in the ablation zone is a low peak temperature. In an alternative to the third preferred ablation probe tip, the coaxial antenna is preferably a near-field antenna. The ablation center is preferably a stationary ablation center. The near-field antenna preferably prevents the ablation center from migrating up the axis away from the insertion end. An alternative to the third preferred ablation probe tip further includes an annular heat transfer layer surrounding the coaxial antenna. The annular heat transfer layer may surround the coaxial antenna and be separated from the insertion end such that the annular aperture is located between the annular heat transfer layer and the insertion end. The annular heat transfer layer preferably prevents the ablation center from migrating upward along the axis away from the insertion end. In an alternative to the third preferred ablation probe tip, the ablation zone preferably has a predetermined shape selected from the group consisting of oblate, spherical, and oblong. An alternative to the third preferred ablation probe tip further includes an annular heat transfer layer surrounding the coaxial antenna and separated from the insertion end, such that the annular aperture is between the annular heat transfer layer and the insertion end. The ablation zone preferably has a predetermined shape determined by an aperture offset. The aperture offset is preferably a distance between the ablation center and an annular edge of the annular heat transfer layer. An oblate ablation zone preferably has a relatively short aperture offset. An oblong ablation zone preferably has a relatively long aperture offset. A spherical ablation zone preferably has an aperture offset between the aperture offsets of the oblate ablation zone and the oblong ablation zone. An alternative to the preferred third ablation probe tip further includes an annular heat transfer layer surrounding the coaxial antenna. The coaxial antenna further includes an annular insulating layer surrounding the coaxial antenna. The annular heat transfer layer preferably surrounds the annular insulating layer. In an alternative to the third preferred ablation probe tip, an antenna end load is preferably placed between the annular aperture and the insertion end. The antenna end load can concentrate the energy density and increase the power load. An alternative to the preferred third ablation probe tip further includes an annular heat transfer layer surrounding the coaxial antenna and separated from the insertion end, such that the annular aperture is between the annular heat transfer layer and the insertion end. The annular heat transfer layer preferably has high thermal conductivity and is preferably electrically conductive. In an alternative to the third preferred ablation probe tip, the coaxial antenna includes an inner conductor, an annular dielectric insulating layer surrounding the inner conductor, and an outer annular conductor surrounding the annular dielectric insulating layer. The annular aperture exposes an annular ring of the annular dielectric insulating layer. In an alternative to the third preferred ablation probe tip, the ablation probe tip is preferably part of a surgical ablation kit that includes an ablation source, a handpiece, a stent, and a prescription. The prescription preferably includes at least one setting or parameter selected from the group consisting of: ablation energy dose tolerances, energy levels, and energy delivery duration. In an alternative to the preferred third ablation probe tip, the ablation probe tip is preferably used in conjunction with a stent. The stent preferably has a surgical guide. The surgical guide preferably serves to guide the ablation probe tip so that the ablation center is within the tissue. In an alternative to the third preferred ablation probe tip, the coaxial antenna is preferably a near-field reactive antenna. An alternative to the third preferred ablation probe tip further includes an annular heat transfer layer surrounding the coaxial antenna and separated from the insertion end, such that the annular aperture is located between the annular heat transfer layer and the insertion end. Preferably, the annular heat transfer layer blocks the ablation media from migrating upward along the axis away from the insertion end. Preferably, the annular heat transfer layer allows thermal energy from the ablation zone to ascend along the axis away from the insertion end. In an alternative to the third preferred ablation probe tip, the ablation probe tip is preferably part of an ablation probe system that preferably has intraoperative maximum temperature control selected from the group consisting of: passive cooling, active cooling, and a combination of passive and active cooling. An alternative to the preferred third ablation probe tip further includes an annular heat transfer layer surrounding the coaxial antenna and separated from the insertion end, such that the annular aperture is located between the annular heat transfer layer and the insertion end. The annular heat transfer layer is preferably quenched by the transfer of thermal energy from the annular heat transfer layer to the soft tissue surrounding the annular heat transfer layer. In an alternative to the third preferred ablation probe tip, the ablation probe tip is preferably part of an ablation probe system that preferably has intraoperative control of the ablation zone volume. In an alternative to the third preferred ablation probe tip, the ablation probe tip is preferably part of an ablation probe system that preferably has intraoperative control of the ablation zone diameter. In an alternative to the third preferred ablation probe tip, the ablation probe tip and the ablation media together allow at least one selected intraoperative control of the group consisting of: ablation zone position, ablation zone shape, ablation zone centering, maximum ablation zone temperature, ablation zone volume, and ablation zone diameter. As an alternative to the third preferred ablation probe tip, the ablation probe tip is preferably a microablation probe tip. In an alternative to the third preferred ablation probe tip, the ablation probe tip is preferably a microwave ablation probe tip. The microwave ablation probe tip can receive microwave energy from the ablation source as the ablation medium. The microwave energy can be delivered to the target tissue through the ablation probe tip. The ablation source can provide microwave energy at frequencies ranging from 500 MHz to 20 GHz. In an alternative to the third preferred ablation probe tip, the ablation probe tip is preferably a radiofrequency ablation probe tip. A fourth preferred ablation probe tip preferably has a shaft with an insertion end. The ablation probe tip preferably receives ablation media from an ablation source. The ablation probe tip preferably serves for the ablation of the target tissue. The ablation probe tip preferably includes: the shaft, an annular aperture, and an ablation center. The shaft preferably includes a coaxial antenna. The annular aperture is preferably defined in at least one outer layer of the coaxial antenna toward the insertion end. The ablation center is preferably located within the coaxial antenna and is surrounded by the annular aperture. The ablation center can be considered a focal region from which the ablation media radiate through the annular aperture to form an ablation zone.The ablation zone preferably has an annular opening and a maximum temperature in the ablation zone, the annular opening and maximum temperature selected from the group consisting of: (i) a short annular opening and a high peak temperature; (ii) a medium annular opening and a medium peak temperature; and (iii) a long annular opening and a low peak temperature. In an alternative to the preferred fourth ablation probe tip, the ablation zone selectively ablates the target tissue while mitigating damage to immediately adjacent collateral tissues. In another alternative to the preferred fourth ablation probe tip, the ablation zone destroys at least part of the target tissue. In an alternative to the preferred fourth ablation probe tip, the coaxial antenna is preferably a near-field antenna. The ablation center is preferably a stationary ablation center. The near-field antenna preferably prevents the ablation center from migrating up the axis away from the insertion end. An alternative to the preferred fourth ablation probe tip further includes an annular heat transfer layer surrounding the coaxial antenna. The annular heat transfer layer may surround the coaxial antenna and be separated from the insertion end such that the annular aperture is located between the annular heat transfer layer and the insertion end. The annular heat transfer layer preferably prevents the ablation center from migrating upward along the axis away from the insertion end. In an alternative to the fourth preferred ablation probe tip, the ablation zone preferably has a predetermined shape selected from the group consisting of oblate, spherical, and oblong. An alternative to the preferred fourth ablation probe tip further includes an annular heat transfer layer surrounding the coaxial antenna and separated from the insertion end, such that the annular aperture is between the annular heat transfer layer and the insertion end. The ablation zone preferably has a predetermined shape determined by an aperture offset. The aperture offset is preferably a distance between the ablation center and an annular edge of the annular heat transfer layer. An oblate ablation zone preferably has a relatively short aperture offset. An oblong ablation zone preferably has a relatively long aperture offset. A spherical ablation zone preferably has an aperture offset between the aperture offsets of the oblate and oblong ablation zones. An alternative to the preferred fourth ablation probe tip further includes an annular heat transfer layer surrounding the coaxial antenna. The coaxial antenna further includes an annular insulating layer surrounding the coaxial antenna. The annular heat transfer layer preferably surrounds the annular insulating layer. In an alternative to the preferred fourth ablation probe tip, an antenna end load is preferably placed between the annular aperture and the insertion end. The antenna end load can concentrate the energy density and increase the power load. An alternative to the preferred fourth ablation probe tip further includes an annular heat transfer layer surrounding the coaxial antenna and separated from the insertion end, such that the annular aperture is between the annular heat transfer layer and the insertion end. The annular heat transfer layer preferably has high thermal conductivity and is preferably electrically conductive. In an alternative to the preferred fourth ablation probe tip, the coaxial antenna includes an inner conductor, an annular dielectric insulating layer surrounding the inner conductor, and an outer annular conductor surrounding the annular dielectric insulating layer. The annular aperture exposes an annular ring of the annular dielectric insulating layer. In an alternative to the fourth preferred ablation probe tip, the ablation probe tip is preferably part of a surgical ablation kit that includes an ablation source, a handpiece, a stent, and a prescription. The prescription preferably includes at least one setting or parameter selected from the group consisting of: ablation energy dose tolerances, energy levels, and energy delivery duration. In an alternative to the preferred fourth ablation probe tip, the ablation probe tip is preferably used in conjunction with a stent. The stent preferably has a surgical guide. The surgical guide preferably serves to guide the ablation probe tip so that the ablation center is within the tissue. As an alternative to the preferred fourth ablation probe tip, the ivia / t / zuzz / uiu 11 υ coaxial antenna is preferably a near-field reactive antenna. An alternative to the preferred fourth ablation probe tip further includes an annular heat transfer layer surrounding the coaxial antenna and separated from the insertion end, such that the annular aperture is between the annular heat transfer layer and the insertion end. Preferably, the annular heat transfer layer prevents the ablation media from migrating upward along the shaft, away from the insertion end. Preferably, the annular heat transfer layer allows thermal energy from the ablation zone to travel upward along the shaft, away from the insertion end. In an alternative to the fourth tip of the preferred ablation probe, the ablation probe tip is preferably part of an ablation probe system that preferably has intraoperative control of the maximum temperature selected from the group consisting of: passive cooling, active cooling, and a combination of passive and active cooling. An alternative to the preferred fourth ablation probe tip further includes an annular heat transfer layer surrounding the coaxial antenna and separated from the insertion end, such that the annular aperture is located between the annular heat transfer layer and the insertion end. The annular heat transfer layer is preferably quenched by the transfer of thermal energy from the annular heat transfer layer to the soft tissue surrounding the annular heat transfer layer. In an alternative to the preferred fourth ablation probe tip, the ablation probe tip is preferably part of an ablation probe system that preferably has intraoperative control of the ablation zone volume. In an alternative to the preferred fourth ablation probe tip, the ablation probe tip is preferably part of an ablation probe system that preferably has intraoperative control of the ablation zone diameter. In an alternative to the preferred fourth ablation probe tip, the ablation probe tip and the ablation means together allow at least one selected intraoperative control of the group consisting of: ablation zone position, ablation zone shape, ablation zone centering, maximum ablation zone temperature, ablation zone volume, and ablation zone diameter. As an alternative to the fourth preferred ablation probe tip, the ablation probe tip is preferably a microablation probe tip. In an alternative to the fourth preferred ablation probe tip, the ablation probe tip is preferably a microwave ablation probe tip. The microwave ablation probe tip can receive microwave energy from the source of ML / IZ / ZZZZ / υUII and ablation as the ablation method. Microwave energy can be delivered to the target tissue through the tip of the ablation probe. The ablation source can provide microwave energy at frequencies ranging from 500 MHz to 20 GHz. In an alternative to the fourth preferred ablation probe tip, the ablation probe tip is preferably a radiofrequency ablation probe tip. The objectives, features, combinations, and advantages described and implied herein will be more easily understood by considering the following detailed description of the invention, taken in conjunction with the accompanying drawings. The subject matter described herein is also specifically noted and clearly claimed in the final part of this specification. DESCRIPTION OF THE DRAWINGS The accompanying drawings illustrate several exemplary ablation probe systems, components of several exemplary ablation probe systems, and / or provide teachings by which the various exemplary ablation probe systems are more easily understood. Figure 1A is a simplified block diagram of an ablation probe system, a custom physical surgical stent, and a soft tissue ablation site. Figure 1B is a simplified visualization showing the virtual marks of the surgical guide angle, a virtual stop mark, and the virtual target marks that guide a representation of a sensor handpiece and the ablation probe tip. Figure 2 is a simplified cross-sectional view of an exemplary soft tissue ablation site within an oral cavity, the ablation probe tip positioned by the stent such that the ablation center is within the soft tissue. Figure 3 is a simplified cross-sectional view of an exemplary soft tissue ablation site within an oral cavity, the ablation probe tip positioned by the endoprosthesis such that the ablation center is within the soft tissue, the radiating arrows represent an exemplary ablation zone. Figure 4 is a cross-sectional view of a tissue having a medium with radiating arrows representing an exemplary ablation zone and the oval outline representing the predetermined outer limits of the ablation zone. Figure 5 is a cross-sectional computed tomography (CT) image of an axial view of a dental tooth. Figure 6 is a cross-sectional CT image of a coronal view of a tooth. ivia / t / zuzz / uiu 11 υ Figure 7 is a cross-sectional CT image of a sagittal view of a tooth. Figure 8 is a cross-sectional view of an ablation probe. Figure 9 is a cross-sectional view of an ablation probe and three different predetermined ablation zone shapes. U11 a Figure 10 is a cross-sectional view of an ablation probe and an exemplary energy flow. Figure 11 is a cross-sectional view of an ablation probe and an oblate ablation zone. Figure 12 is a cross-sectional view of an ablation probe and a spherical ablation zone. Figure 13 is a cross-sectional view of an ablation probe and a zone of oblong ablation. Figure 14A is a graphical representation of an ablation probe and an oblate heating pattern (aspect ratio > 1.0) resulting in an oblate soft tissue ablation zone. Figure 14B is a graphical representation of an ablation probe and a spherical heating pattern (aspect ratio = 1.0) resulting in a spherical soft tissue ablation zone. Figure 14C is a graphical representation of an ablation probe and an oblong heating pattern (aspect ratio < 1.0) resulting in an oblong soft tissue ablation zone. Figure 15A is a photographic representation of an ablation probe and an oblate heating pattern (aspect ratio > 1.0) resulting in an oblate soft tissue ablation zone. Figure 15B is a photographic representation of an ablation probe and a spherical heating pattern (aspect ratio = 1.0) resulting in a spherical soft tissue ablation zone. Figure 15C is a photographic representation of an ablation probe and an oblong heating pattern (aspect ratio < 1.0) resulting in an oblong soft tissue ablation zone. Figure 16A is a photographic representation showing the adverse impact of using conventional medical ablation at 2.45 GHz resulting in an oblong soft tissue ablation zone. Figure 16B is a photographic representation showing an ablation zone produced at a higher frequency (8 GHz) resulting in an oblong, teardrop-shaped soft tissue ablation zone. Figure 16C is a photographic representation showing a spherical ablation zone (measured at sixty degrees Celsius (60 °C)) generated using the dental outline ablation probe described herein. Figure 17 shows the results of an exemplary sounding experiment related to roundness at sixty degrees Celsius (60 °C). Figure 18 shows the effects of power and time on the cross-sectional ablation zone area in an exemplary model describing the ablation volume. Figure 19 is a simplified view showing an ablation probe that maintains a stationary ablation center without asymmetric migration of the ablation zone toward the probe tip axis. Figure 20A is a photographic representation of an ablation probe with the soft tissue ablation center generating temperatures above one hundred degrees Celsius (100 °C), the steam generated as a result is shown as the wavy rings. Figure 20B is a photographic representation of an ablation probe with the soft tissue ablation center generating temperatures that remain below one hundred degrees Celsius (100°C), the rings being more regular as steam is not present. Figure 21 is a photographic representation showing an under-ablation zone, a correct ablation zone, and an over-ablation zone. Figure 22 shows the results of an exemplary probe experiment that correlates the diameter of the ablation zone (in mm) with the duration of ablation (in seconds). Figure 23A is a graphical representation of an ablation probe with a short annular aperture (which delimits a small focal region) and a short active heating zone that creates a high power load in the ablation zone. Figure 23B is a graphical representation of an ablation probe with a medium annular aperture (which delimits a medium focal region) and a medium active heating zone that creates a medium power load in the ablation zone. Figure 23C is a graphical representation of an ablation probe with a long annular aperture (which delimits a large focal region) and a long active heating zone that creates a low power load in the ablation zone. Figure 24A is a photographic representation of an ablation probe with a small focal region that creates a high-power load in the ablation zone. Figure 24B is a photographic representation of an ablation probe with a medium focal region that creates a medium power load in the ablation zone. U11 a Figure 24C is a photographic representation of an ablation probe with a large focal region that creates a low-power load in the ablation zone. The figures in the drawing are not necessarily to scale. Certain features or components may be shown somewhat schematically, and some details of conventional elements may be omitted or not described for the sake of clarity and conciseness. For example, although a dental sketch is shown, any soft tissue may be considered. The figures in the drawing are hereby incorporated into and form part of this specification. DETAILED DESCRIPTION This disclosure describes devices, methods / procedures, and systems generally pertaining to the technical field of medical ablation probes. Some of the preferred devices, methods / procedures, and systems described herein specifically pertain to the technical field of microwave ablation (MA) and radiofrequency ablation (RFA) probes that provide controlled zones of soft tissue ablation. Although the devices, methods / procedures, and systems can be applied to any type of target tissue, dental outlines will be used as the exemplary target tissue throughout this document. The ablation probe system (also referred to as dental outline ablation technology or microablation technology) described herein allows the operator to precisely control at least one or more intraoperative parameters to achieve predictable clinical outcomes. Specific intraoperative controls include: I. Image-guided volume scanning positioning control (also referred to in this document as ablation zone positioning control or positioning control); II. Ablation zone shape control (also called ablation zone shape control or ablation shape control); III. Ablation center control (also called center-directed ablation control); IV. Temperature control of the ablation zone; V. Guided control of the ablation volume / diameter (also called ablation zone volume / diameter control); and VI. Power load control (also called power density control). The control of various combinations of these controls and their respective ML / E / ZuZz / uU11 9 parameters results in highly selective ablation of target tissues, while mitigating damage to immediately adjacent collateral tissues. The ablation probe system, as described herein, can be implemented as microablation surgical kits (also referred to as surgical kits, ablation surgical kits, or microablation kits) that preferably contain a patient-specific microablation probe (which may or may not be disposable) and a patient-specific high-precision surgical guide (which may be a disposable physical guide, as shown in Figure 1A, or a virtual guide, as shown in Figure 1B) used to position the probe during ablation. The high-precision surgical guide is preferably suitable for directing the ablation center of the microablation probe into (and preferably the center of) the tissue.Surgical kits may also include a prescription that specifies the ablation energy dose tolerances and settings (e.g., energy level and duration of energy delivery) required to ablate the target or predetermined soft tissue volume. Microablation kits may include and / or be used with an ablation source (e.g., a smart microablation generator) and a handpiece. The devices, methods / procedures, and systems described here produce heated zones (ablation zones) that result in a defined volume of tissue hyperthermia. This focal hyperthermia induces a selective zone of cell death due to localized thermocoagulative necrosis, leading to tooth agenesis when a sufficient volume of tissue from the tooth bud has been destroyed (i.e., killing the cells but destroying the tissue). Therefore, ablation removes or destroys the predetermined target tissue, causing minimal damage to surrounding tissue or structure, compared to more invasive conventional surgical techniques. Once the target tissue is destroyed, the body's normal healing mechanisms will eliminate the destroyed tissue. Live animal trials of tooth bud ablation using the devices, methods / procedures, and systems described herein have delivered microwave energy to soft tissue at frequencies ranging from 500 MHz to 20 GHz. The results of these trials have shown 100% success in ablating target tissue areas and achieving clinically induced complete molar agenesis with limited damage to adjacent non-target tissues. Furthermore, healing is excellent, with all dead tissue removed, bone completely refilled, and no signs of tooth formation from the target lesion observed 4–6 weeks post-treatment. The test results demonstrate that the use of the ablation probe system will allow dentists to perform tooth bud ablation treatments in 20–40 seconds. MLE / E / ZUZZ / Ul Ul 1U highly controlled when at least one of the intraoperative controls of the ablation probe system is employed. The microablation technology described here is considered unique because it is the only known medical microablation process with the ability to simultaneously control the positioning, shape, centering, maximum temperature, and volume and / or diameter of the target ablation tissue. The preferred ablation probe systems (50) described herein have many potential advantages. Some potential preferred advantages include, but are not limited to, the following: • Due to the heat transfer mechanisms, the preferred ablation probe systems (50) can produce ablation times of 20-40 seconds without overheating the tissue (and thus avoiding tissue charring) with the possibility that longer ablation times can be used when employing lower power densities (power load) or when prescribing larger ablation volumes. • The energy dose delivered by the preferred ablation probe systems (50) can be monitored and controlled for repeatability under a wide range of clinical conditions and operator skills. • The preferred ablation probe systems (50) have ablation probe tips (100) (also referred to as probe tips (100), microablation probe tips (100), and microablation ablation probe tips (100)) with shafts having a diameter of 3.8 mm (the diameter of a 7-gauge needle) down to 1.0 mm or less (the diameter of a 20-gauge needle) for applications requiring those small dimensions. • Because the probe ablation center (124) (focal region (124)) is stationary (the ablation center (124) does not migrate during treatment), the predetermination of the outer margins of the ablation zone (150, 160, 170) to encompass only the target tissues (e.g., at least part of a tooth outline (92)) becomes significantly more predictable, while reducing the risk of ablation of the surrounding tissue. The ablation center (124) (focal region (124)) is predetermined and, being stationary, its location remains known. The location of the active heating zone (125) surrounding the focal region (124) (and the peak tissue temperatures within the active heating zone (125)) are therefore significantly more predictable. When operating at a known power, the predictability of the active heating zone (125) at least reduces (and possibly eliminates) the charring of the tissue into an undefined, black mass, which, in turn, reduces (and possibly eliminates) the risk of adverse postoperative scarring. Before describing the ablation devices, methods / procedures, and systems, and the Figures, it is necessary to clarify some terms. Note that terms and phrases may have additional definitions and / or examples throughout this specification. When not specifically defined, words, phrases, and acronyms are used according to their ordinary meaning in the art. The following paragraphs provide basic parameters for interpreting the terms and phrases used herein. The term tissue refers to any of the various types of material that make up people or animals, composed of specialized cells and their products. Tissue can be soft tissue. The phrase target tissue (also called objective tissue) refers to the tissue that is to be ablated. An example of target tissue might be a tooth bud or a tumor. The phrase surrounding tissue describes the tissue that surrounds the target tissue and should not be ablated. • The term center (used in the phrases center of dental prototypes or center of tissue) is intended to describe a position within the target tissue (e.g., a dental prototype). The center is not necessarily the absolute center of the tissue. The calculated center of the tissue to be ablated can be determined using methods that include, but are not limited to, those that utilize volume, three-dimensional position, and / or other known or yet-to-be-discovered methods. A predetermined center (or predetermined position) may be the calculated center of the tissue to be ablated or may simply be a known position within the tissue to be ablated. Unless specifically stated otherwise, when referring to the center, a calculated and / or predetermined center within the fabric may be used. • The term ablation zone (also called soft tissue ablation zone, controlled soft tissue ablation zone, ablation zone, heating zone, and temperature control zone) is intended to describe the area in which ablation will be or has been created. Ideally, the ablation zone is substantially coextensive with the target tissue. The target tissue can also be considered the target ablation zone. The ablation zone has a three-dimensional area or volume, although the photos and drawings in this document may make it appear as a two-dimensional image. • The term microablation refers to ablations less than 25.00 mm in diameter for use on smaller anatomical structures, such as a tooth bud, although larger ablations can be used on tumors larger than 5 cm in diameter. In the case of microablations, the probe tip (100) would be a microablation probe tip. Unless otherwise specified, the phrase probe tip includes microablation probe tips. • The phrase ablation means (as in ablation means (62)) ML / E / ZuZZ / uU11 is intended to describe the mechanism (e.g., energy) by which ablation or microablation is performed. The preferred ablation means may be energy such as microwaves (MW) and / or radiofrequency (RF), and in particular, microwave ablation energy in the range of 500 MHz to 20 GHz (wide spectrum) and radiofrequency ablation energy in the range below 500 MHz. This range would include both microwave and radiofrequency ablation energy. The ablation means (62) are provided by an ablation source (60). • The phrase ablation source (as in ablation source (60)) is intended to describe the mechanism by which the ablation media are produced. The ablation source (60) may be a purpose-built ablation source, such as a smart microablation generator. The ablation source may be a generator and / or an amplifier (collectively referred to as a generator). If the ablation media (62) are microwave ablation media, the ablation source (60) may be a microwave generator. If the ablation media (62) are radiofrequency ablation media, the ablation source (60) may be a radiofrequency generator. If the ablation source (60) is a smart generator, it may be programmed with the procedure parameters (e.g., time, temperature, energy delivery rate, frequency, and other parameters) and can then deliver the ablation media to the target tissue based on those parameters.A smart generator may have built-in error-checking and safety features. For example, a smart generator can check for faulty probe tips (100) by measuring forward and reflected power / energy to determine the total power / energy (energy / time) delivered to the ablation zone. If the smart generator cannot reach and / or maintain the prescribed energy level, the procedure stops and an error message is generated. • The phrases ablation center and focal region are intended to describe the portion of the internal conductor (112) that is bounded by the annular aperture (120) from which the ablation media (62) radiate. An active heating zone (125) surrounds the focal region (124). Around the active heating zone (125) is an ablation zone (150, 160, 170). As shown in Figures 23A to 23C, for example, the area of ​​the ablation zone (160a, 160b, 160c) (which are variations of the spherical ablation zone (160)) beyond the active heating zone (125) is a thermal heating zone (126) (created by thermal conduction). • The terms active heating zone, active tissue heating zone, active tissue heating zone, active heating zone, and variations thereof refer to the description of the target tissue within the ablation zone (150, 160, 170) into which the ablation medium (62) initially enters. As shown in Figures 23A to 23C, for example, the active heating zone (125) is at least substantially annular and adjacent to the annular opening (120) of the probe tip (100). The active heating zone (125) is where radiant energy is converted to thermal energy.Tissue within the ablation zone (150, 160, 170) that is outside the active heating zone (125) (i.e., within the thermal heating zone (126)) continues to undergo cell death, but cell death within the thermal heating zone (126) is caused by heat being conducted outwards from the active heating zone (125). The terms power load, power density, power load density, and volume power density describe the amount of energy (e.g., microwave or radio frequency energy) as a function of time (power being a unit of energy delivered per unit of time) supplied to the active heating zone (125). For example, a dipole antenna (a longer, lower-power-load antenna) with no end load and less capacitive coupling will generally be two to four times longer than the shorter, higher-power-load end-load antenna shown (e.g., an ablation probe tip (100) with an end load 122). In this example, microwave energy is propagated along the longer antenna in a predefined manner before radiating into the active heating zone (125).The propagation of energy in the longer antenna results in a power load density in the active heating zone (125) that is two to four times lower compared to the higher power load in the shorter antenna that provides the same amount of energy per unit of time. • The term profile (as used in the phrases ablation zone profile, probe profile, ablation profile, probe ablation profile and ablation zone margins or ablation zone tissue margins) refers to the description of the known attributes and variables of the ablation zone associated with a particular ablation probe system (50) and / or the ablation zones (150, 160, 170) that it produces in soft tissues.These attributes and variables include, but are not limited to, the shape (e.g., oblate, spherical, oblong) of the ablation zone produced by the ablation probe system (50), the size (e.g., dimensions and volume) of the ablation zone produced by the ablation probe system (50), the location of the ablation zone along the length of the probe tip (100), the temperature of the ablation zone produced by the ablation probe system (50), and the time (duration) it takes the ablation probe system (50) to produce the ablation zone. These attributes and variables may be interrelated. For example, the size of the ablation zone produced by the ablation probe system (50) may be directly related to the amount of ablation medium (62) (e.g., microwave energy) used and the duration of use of the ablation medium (62). Using an ablation probe system (50) with the appropriate profile, the appropriate input, and the appropriate duration will produce the desired ablation zones (150, 160, 170). • The term "volume scanning" (as well as "volume scanning" and other variations used herein) is intended to include any known or yet-to-be-discovered volume scanning technology that, at least with relative certainty, accurately generates the necessary multidimensional images for use in medical procedures. Exemplary volume scanning imaging includes, but is not limited to, computed tomography (CT) (e.g., cone-beam computed tomography (CBCT)), X-ray, magnetic resonance imaging (MRI), ultrasound, nuclear medicine imaging (e.g., positron emission tomography (PET)), and other types of three-dimensional volume or soft tissue scanning imaging that may be used or adapted to implement the functions described herein.The phrase and its variations can be used as a noun (e.g., the image) or as a verb (the process of taking the image). Whether the phrase is used as a noun or a verb can be determined from the context in which it is used. The term "image" is intended to describe both the process of acquiring an image and the image itself, the difference being evident from the context. The image may be a volume scan image, such as a cone-beam image (produced, for example, by a computed tomography (CT) scan (e.g., a cone-beam computed tomography (CBCT) scan), an X-ray image, a magnetic resonance imaging (MRI) image, an ultrasound image, a nuclear medicine image (e.g., a positron emission tomography (PET) scan), or any known or yet-to-be-discovered imaging medium that can display the target tissue and surrounding tissue in sufficient detail to permit the use of the system and methods described herein. In some cases, a specific type of image is suggested, but other images may be used if they can serve the same purpose.For example, panographic images are suggested for routine screening of tooth buds, but other known or yet-to-be-discovered imaging techniques could be used for screening tooth buds and for measuring soft tissue dimensions of tooth buds. When used as a verb, the term "imaging" refers to the process of taking an image as described above. U11 a The electromagnetic fields around objects such as antennas can be divided into regions that include the near field (which can be further divided into non-radiative (reactive) and radiative (Fresel)) and the far field. Non-radiative near-field behaviors dominate near the antenna, while far-field behaviors dominate at greater distances. In near-field regions, interference occurs in the propagation of electromagnetic waves, and therefore, near-field regions are considered unpredictable. Conversely, in far-field regions, the field acts as a normal with a relatively uniform wave pattern. The ablation probe systems (50) described herein are preferably designed to operate in the near-field region. The ablation system described herein may have associated hardware, software, and / or firmware (a variation, subset, or hybrid of hardware and / or software). The term hardware includes at least one processing unit, processor, computer, programmable device, and / or other known or yet-to-be-discovered devices capable of executing instructions or steps. The term software includes at least one program, subprogram, instruction set, or other known or yet-to-be-discovered hardware instructions or hardware-readable program code. An example of software includes the surgical endoprosthesis design software suite described herein. The software may be loaded onto the hardware (e.g., the ablation source (60)) to produce a machine, such that the software runs on the hardware to create structures for implementing the functions described herein.Furthermore, the software can be loaded onto the hardware (e.g., the ablation source (60)) to direct the ablation probe system (50) to operate in a particular manner described herein or to perform a series of operational steps as described herein. The phrase "loaded onto the hardware" also includes being loaded into memory associated with or accessible by the hardware (including firmware).The term memory (e.g., ablation source memory (60)) is defined to include any type of hardware-readable (or other technology-readable) medium (also called machine-readable storage medium), including, but not limited to, attached storage media (e.g., hard disk drives, network disk drives, servers), internal storage media (e.g., RAM, ROM, EPROM, FLASH-EPROM, or any other memory chip or cartridge), removable storage media (e.g., CDs, DVDs, flash drives, memory cards, floppy disks, diskettes), firmware, and / or other storage media known or yet to be discovered. Depending on its purpose, memory may be transient and / or non-transient. Appropriate communications, signals, and / or transmissions (including various types of information and / or instructions, including, but not limited to, data, commands, bits, symbols, etc.) are also included. ML / IZ / ZZZZ / υΊ U11» voltages, currents, electromagnetic waves, magnetic fields or particles, optical fields or particles, and / or any combination thereof) through appropriate communication channels,” transmission channels and other means for signal transmission, including any type of connection between two elements of the system (the system, including, for example, the ablation source (60), the handpiece (52), the ablation probe tip (100), other hardware systems and / or subsystems, and / or memory) would be used as appropriate to facilitate controls and communications. • The term associated (and variations such as associable), when used in the context of a connection between components, is defined as integral or original, retrofitted, attached, connected (including functionally connected), positioned nearby, and / or accessible by. For example, if a display (such as the output mechanism (68) or another component) is associated with a computer (including a processor associated with the ablation source (60) or other technology), the display may be an original display integrated into the computer, a display that has been retrofitted to the computer, an attached display that is joined to the computer, a nearby display that is positioned close to the computer, and / or a display that is accessible by the computer.Another example is the connection between the ablation source (60), the handpiece (52), and the ablation probe tip (100) are described as associable in the sense that the connections between these elements can be integral or original, retrofitted, attached, connected (including functionally connected), positioned close, and / or accessible by. • The terms "may," "could," "may," and "could" are used to indicate alternatives and optional features and should only be construed as a limitation if specifically included in the claims. It should be noted that the various components, features, steps, designs, or embodiments thereof are all preferred, whether or not specifically stated. Claims that do not include a specific limitation should not be construed as including that limitation. • Unless specifically stated otherwise, the term "exemplary" indicates an example, representation, and / or illustration of a type. The term "exemplary" does not necessarily mean the best or most desirable of the type. It should be noted that, unless otherwise specified, the term "or" is used in its non-exclusive form (e.g., A or B includes, but is not limited to, A, B, A and B, or any combination thereof). It should be noted that, unless otherwise specified, "and / or" is used similarly (e.g., A and / or B includes, but is not limited to, A, B, A and B, or any combination thereof). It should be noted that, unless otherwise specified, the terms "includes," "has," and "contains" (and variations of these terms) mean ML / E / ZuZz / uIIU comprises (for example, a device that includes, has or contains A and B, comprises A and B, but may optionally contain C or additional components other than A and B). It should be noted that, unless otherwise specified, the singular forms a, an, and the refer to one or more than one, unless the context clearly dictates otherwise. Similarly, unless specifically limited, the use of singular language (e.g., component, module, or step) may include plurals (e.g., components, modules, or steps), unless the context clearly dictates otherwise. L Scanner-guided volume positioning and ablation control Volume scanning, as described herein, is any scanning technology that can reliably and accurately generate the necessary multidimensional images for use in ablation procedures. Volume scanner-guided positioning and ablation control is also referred to as volume scanner-guided control and volume scanner-guided procedures. Volume scanner-guided positioning and ablation control includes volume scanner-guided positioning control, volume scanner-guided ablation control, and volume scanner-guided soft tissue ablation.Volume scan-guided control is a technology for precisely positioning the tip of an ablation probe and then ablating the desired soft tissue by delivering a predetermined amount of energy based on the soft tissue dimensions measured in the volume scan. Positioning can be performed physically using a physical stent, as shown in Figure 1A, and / or virtually using a virtual stent, as shown in Figure 1B. Ablation can be performed by heating a predetermined volume of soft tissue through controlled energy delivery. Such physical and virtual endoprostheses are described in the therapeutic properties of ablation of the dental outline.For example, the creation of a custom surgical stent using location and measurement information on dental outlines obtained from a scanner is described in Properties of Therapeutic Ablation of Dental Outlines, as well as in this document. Volume scan-guided positioning control (e.g., a stent) can be created from preoperative measurements obtained using volume scan technology. Exemplary steps for creating a stent include, but are not limited to: • Select an ablation probe tip (which may be a sensorized ablation probe tip) with known dimensions and capacities. Information about the dimensions and capacities can be stored in a volume scan information technology file (e.g., a computer-aided three-dimensional design file). ΜΛ / Ε / ΖυΖΖ / υΊ U11y (CAD)). • Using volume scanning technology, scan a patient's mouth. The information (including a volume scan image) from the volume scan can be stored in a scan technology file (e.g., the volume scan information technology file). • From the volume scan, create physical (traditional) or digital impressions of the patient's teeth and gingival tissue. If a digital impression is created, it can be stored in a data file from the volume scanner. • From the volume scan or the volume scan information file, obtain (e.g., calculate and / or measure) the size and position of the dental outlines using the information from the volume scan information file. Information on the size and position of the dental outlines can be stored in a volume scan information file. • Using the volume scan or the volume scan information file, locate a landmark (e.g., the distal side of the first erupted molars or the soft tissue overlying the bone). Information about the landmark's location relative to the tooth outline can be stored in a volume scan information file. • From the volume scan or the information in the volume scan technology file, locate or obtain (e.g., calculate and / or measure) the center of the dental outlines (calculated center) or at least one position within the dental outlines (a predetermined position). Information about the center of the dental outlines can be stored in a scan technology file. • From the volume scan or the volume scan information technology file, obtain (e.g., calculate and / or measure) a predetermined angle (the angle at which the effective ablation center of the ablation probe tip is at the center of the dental outline—shown as 90 degrees in Figure 2) to guide the ablation probe tip. The angle can be calculated or measured from a known point (e.g., the landmark or entry point, taking into account the thickness and surface of a physical stent and the shape of the ablation probe tip) to the center of the dental outlines. The predetermined angle information can be stored in a scan technology file. • From the volume scan or the information in the volume scan technology file, obtain (e.g., calculate and / or measure) the ML / E / ZuZZ / uU11y default depth (the depth at which the effective ablation center of the ablation probe tip is located in the center of the tooth outline) to limit the depth of the ablation probe tip. The depth can be calculated or measured from a known point (e.g., the landmark or entry point, taking into account the thickness and surface of a physical stent and the shape of the ablation probe tip) to the center of the tooth outlines. In Figure 2, depth D is shown as the distance between the upper surface of the gingival tissue and the ablation center, or alternatively, depth D + D' is shown as the distance between the upper surface of the endoprosthesis and the ablation center. If there is a raised mechanical stop (as shown in Figure 1A), its height can also be added to the depth. Information about the default depth can be stored in a scan technology file. • Processing the information in the volume scan technology file(s) (which may be one or multiple files) to put the information into a form that can be used to create or manufacture a stent (physical or virtual) and to create a prescription that indicates the tolerances and adjustments for the ablation energy dose (e.g., energy level and duration of energy delivery) in order to be guided in the selective ablation of the target tissues. Creation includes manufacturing, so both the virtual and physical endoprosthesis are created, but only the physical endoprosthesis is manufactured. Depending on what is being created, creation (and its variations) may also include programming, collection, or other forms of creation. • Create or fabricate a stent (virtual or physical) with at least one surgical guide (virtual or physical) to guide the ablation probe tip at the predetermined angle and at least one stop structure (virtual or physical) to limit the depth of the ablation probe tip to the predetermined depth. If the stent is physical, it may have a mechanical stop structure that interacts with the mechanical stop structure of the stent. Using the surgical guide of the endoprosthesis and the mechanical stop structure, the ablation probe tip can be guided in such a way that the ablation center is within the tooth outline (and, preferably, in the middle of the tooth outlines) when the ablation probe tip is guided at the predetermined angle to the predetermined depth. Figures 1A, 1B, 2 and 3 show a basic system that uses volume scan-guided positioning controls (shown as a physical stent (80) or a virtual stent (82', 86', 88')) to properly position ablation probe systems (50) (including probe tip (100)) that provide shaped target tissue ablation, ML / E / ZuZz / uU11» centered, with controlled temperature and / or with controlled volume. Volume scan-guided procedures precisely position the microablation probe to ensure that tooth bud tissue is heated from the inside (even from the center) of the tooth bud outward to a defined volume with ablation margins of the surrounding soft tissue in the desired location. This achieves safe and effective ablation of the tooth bud while minimizing damage to collateral tissues adjacent to the bud. No competing technology is known to have this level of precision for three-dimensional (3D) positioning of the ablation zone and to maintain the zone in position throughout the procedure. Although some exemplary ablation probe systems (50) and their components are described in more detail herein, Figures 1A, 1B, 2, and 3 provide an overview of an exemplary ablation probe system (50) as used in an exemplary application (dental outline ablation). The ablation probe system (50) can work in conjunction with a customized surgical stent (the physical stent (80) shown in Figure 1A or the virtual endoprosthesis (82', 86', 88j) shown in Figure 1B) at a dental outline ablation site (90). Robotics could also be used in volume scan-guided soft tissue ablation, with robotics serving as a guidance system that can be used with either a physical or virtual system. Some exemplary physical and virtual guides are described in the Properties of Therapeutic Ablation of Dental Outlines. For procedures other than dental outline ablation, where the ablation site might be a location on the body that covers any target tissue, an appropriate surgical stent could be used to guide the placement of the probe tip. For example, if the tumor were in a leg, an appropriate physical or virtual leg stent would be used. As shown in Figure 1A, an ablation probe system (50) (or ablation probe (50)) includes an ablation probe tip (100), a handpiece (52), and an ablation source (60) that provides and / or facilitates the provision of an ablation medium (62). The ablation probe tip (100) may be integral with, connectable (directly or indirectly), or otherwise associated with the handpiece (52). The handpiece (52) may be integral with, connectable (directly or indirectly), or otherwise associated with the ablation source (60). The handpiece (52) may be autoclavable. One type of indirect connection could include the use of a wire or cable that functionally connects the components. Another type of indirect connection could include remote control mechanisms (e.g., appropriate transmitters and receivers) that functionally connect the components. Figures 1A, 2 and 3 show scan-guided positioning control The ML / IZ / ZZZZ / υUII and volume implemented as a custom surgical stent (80) having at least one surgical guide (82) (shown as darkened solid lines through the surgical stent (80) in Figure 1A) and a mechanical stent stop (86) (which, as shown in Figure 1A, may be a raised portion of the stent (80) at least relatively adjacent to the surgical guide (82) or, as shown in Figures 2 to 3, only the top surface of the stent (80) at least relatively adjacent to the surgical guide (82)). The stent (80), guide (82), and stop (86) together constitute a volume scan-guided positioning control form created by the process described herein. Figures 2 to 3 show that at least part of the surgical stent (80) may be at least partially supported by at least one erupted tooth.The custom surgical stent (80) is positioned so that a surgical guide (82) covers and / or surrounds the tooth buds (92) at the tooth bud ablation site (90) (including gingival tissue (94) and bone (96) (including dense cortical bone)). Figure 4 shows the tissue (e.g., a tooth) with a center (93) with radiating arrows representing an exemplary ablation zone and the oval outline representing the predetermined outer limits (98) of the ablation zone. The ablation probe tip (100) (shown in Figure 1A with solid lines before insertion and dashed lines after insertion) has a mechanical tip stop (106) and an ablation center (124). The ablation probe tip (100) can be inserted through the gingival tissue (94) and into the tooth bud (92) (located within the bone (96) of a mandible). The ablation probe tip (100) is guided by the stent (80) so that its insertion end (104) and ablation center (124) are within (e.g., in or near the center (93)) of the tooth buds (92). The interaction between the surgical guide (82) and the tip axis (102) guides the ablation probe tip (100) at the correct angle (shown as a 90-degree or right angle, but it could be other angles) so that the ablation center (124) is within the tooth outlines (92).More specifically, the inner diameter of the surgical guide (82) is slightly larger than the outer diameter of the tip shaft (102), so that the ablation probe tip (100) inserted into the surgical guide (82) can only be inserted at the angle dictated (prescribed) by the surgical guide (82). Limiting the ablation probe tip (100) to the correct depth so that the ablation center (124) is within the tooth outline (92) can be achieved, for example, by the interaction between the mechanical stop of the stent (86) and the mechanical stop of the tip (106) (which may be, for example, a raised surface (Figure 1A), an angled surface, and / or the upper surface (Figures 2-3) of the stent (80)). Preferably, the ablation center (124) is positioned at least substantially in the middle (e.g., the calculated middle) of the tooth outlines (92), as determined by volume, three-dimensional position, and / or other known or yet-to-be-discovered methods. (The calculated or predetermined center of the tissue to be ablated is the center of the tooth outlines (93)). The ablation probe tip (100) is positioned before the ablation means (62) are activated to create the ablation zones (150, 160, 170) (the radiating arrows, although only one type of zone is shown in these Figures, are representative of the different shaped zones shown and discussed here in relation to Figures 9 and 11 to 13). As shown in Figure 3, the predetermined outer limits (98) of the ablation zone are preferably + / - 0.50 mm within the bony crypt of the tooth outlines (92). Figure 1B shows a virtual stent system (82', 86', 88') that can be used with a sensorized ablation probe tip (100') and / or a sensorized handpiece (52j). The virtual stent can be a dynamic navigation technology implemented as at least one software program (or subprogram) associated with the ablation source (60). The program could receive information (e.g., the prescription) and convert that information into a virtual stent. Although the virtual stent could be used on its own, it could also be used in conjunction with a physical stent. For example, it could provide advance warning of approaching parameters (e.g., an audible tip approaching stop) or confirmation (e.g., a flash of light on the handle or a pleasant audible ding when the probe tip is in position).Another example is that the surgical guide could be physically implemented, but the stop and / or target could be implemented virtually. The virtual endoprosthesis system could be displayed on a visual screen (68') with surgical guide angle markings (82)', a virtual stop mark (86j), and virtual target markings (88j) superimposed on an image (e.g., a volume scan) of the area (92') (e.g., the dental outline) to be ablated (for clarity, the actual image has been omitted). Although shown as lines (e.g., dashed lines), alternative visual position indicators could be a digital readout or color coding. The virtual surgical guide angle markings (82') are based on the three-dimensional insertion path (defined by the predetermined angle (e.g., the 90-degree angle shown in Figure 2) and the predetermined depth (e.g., depth D shown in Figure 2)).In the preferred modes, the system could not be activated if the ablation center was not in proper relation to the center of the dental outline. In addition to, or in conjunction with, a physical stent (80) and a virtual stent displayed on a visual screen (68), alternative audible, visual, and / or tactile cues may be used as surgical guidance, stop, and / or target cues. For example, signals (e.g., a series of audible beeps, a series of flashing lights, or physical vibrations) could be used to indicate that the probe tip is approaching the ablation zone. For example, the MA / E / ZUZZ / U1 UII and beeps / flashes / vibrations could become louder / brighter / faster as the probe tip approaches the ablation zone. Alternatively, the indicators could be a voice giving instructions (e.g., “3 mm ... 2 mm ... 1 mm”) or the light could be color-coded (e.g., from red to green). Another example is that the virtual stop and / or virtual target could be implemented audibly, visually, and / or tactilely using similar or different indicators. In use, the sensorized ablation probe tip (100') can be guided by the virtual angle marks on the surgical guide (82)' and the virtual stop mark (86') to a position where the effective ablation center (124') of the ablation probe tip (100') is centered on the tooth outline (93'). The operator can observe the insertion process on the screen (68j) while physically manipulating the sensorized ablation probe tip (100'). The virtual marks (88') can also provide an indication that the sensorized ablation probe tip (100') is within approximately 50%, 25%, and 10% of the mean diameter of the tooth outlines (92j).If the operator were manually manipulating the sensorized ablation probe tip (100'), the system would monitor progress and alert the operator that the ablation probe tip (100') was not in the correct position using, for example, visual indicators, audible indicators, tactile indicators, or a combination thereof. Alternatively, the operator could monitor progress on the screen (68j) as the sensorized ablation probe tip (100') was automatically inserted (for example, using a robotic system). It is preferable that the system include monitoring and override safeguards. For example, the system would not activate if the ablation center was not in the correct relationship to the center of the tooth outline, regardless of whether the insertion was performed manually or robotically. When the probe tip (100) is correctly positioned, the ablation center (124) is within the tooth outlines (92) in its predetermined position. Activation of the ablation means (62) creates an ablation zone (150, 160, 170) (e.g., for a spherical tooth outline (92) (Figure 1A) the appropriate ablation zone would be a spherical ablation zone (160), but for an oblate tooth outline (92) (Figures 2 to 3) the appropriate ablation zone would be an oblate ablation zone (150)) centered around the ablation center (124) within the tooth outlines (92). If the ablation source (60) is a microwave generator, the ablation medium (62) would be microwave energy.The ablation source parameter settings (64) and treatment time settings (66) can be provided by uploading digital data (e.g., downloading the parameter settings (64) and / or the treatment time settings (66) using a patient identification key entered at a provided website address) or can be provided by a user manually entering the data. Feedback from the ablation source (60) or from the ablation probe tip (100) (which may have at least one sensor (108) along the axis (102) to monitor, for example, temperature) may be provided to the user (or to electronic or digital monitoring systems that may be implemented by software associated with an ablation source (60) (for example, a smart generator)) using an output mechanism (68) such as a video display or an audio display (speaker). The cross-sectional images from the volume scanner (in this case, a CT volume scanner) in Figures 5 to 7 show the planned central position of the ablation probe tip (100) within a pig mandibular dental (circled by dashed lines) (similar images could be taken of a human dental). More specifically, Figure 5 shows the axial view of a dental, Figure 6 shows the coronal view of a dental, and Figure 7 shows the sagittal view of a dental. It should be noted that the components in Figure 1A are not to scale (e.g., the ablation probe tip (100) would probably be much smaller than the handpiece (52)). II. Control of the shape of the ablation zone Another capability of the ablation probe system described herein is the shaping of the ablation zone (or the control of the shaping of the ablation zone) within the bony crypt of the tooth. Figures 8 to 18 detail how knowledge of at least one profile of the ablation zones (150, 160, 170) and / or the ablation probe systems (50) (and their method of use) allows the selection of specific ablation probe tips 100 to create predetermined ablation zones that are shaped and / or sized to correspond with the ablation zones of the target tissue. More specifically, Figures 8 to 13 show cross-sections of exemplary probe tips. Figures 14A to C show graphical representations of the ablation probes and their respective ablation zones. Figures 15A to C show photographic representations of the ablation probes and their respective ablation zones. Figures 16A to C show photographic representations of actual ablations. Figure 17 shows the results of an exemplary probe experiment related to roundness. Figures 8 to 13 show exemplary ablation probe tips (100) (including probe tips (100a, 100b, 100c) that are capable of creating ablation zones (150, 160, 170) with predetermined shapes and / or sizes. For example, an ablation probe profile can specify a specific shape U11 as: • oblate (the longest axis of the ablation zone (150) is perpendicular to the axis (102) of the ablation probe tip (100a) as shown in Figure 11, having an aspect ratio greater than 1.0 (oblate ablation zones (150) are wider than they are long); • spherical, as shown in Figure 12, with an aspect ratio of 1.0 (spherical ablation zones (160) are as narrow as they are long); and / or • oblong (the longest axis of the ablation zone (170) is parallel and substantially coexisting with the axis (102) of the ablation probe tip (100c) as shown in Figure 13, which has an aspect ratio less than 1.0 (oblong ablation zones (170) are narrower than they are long). Known microwave ablation probes produce oblong ablation zones that are narrower than they are long (an aspect ratio less than 1.0). These known oblong ablation zones can be so long that they may appear hot dog-shaped along the probe. The oblong ablation zones of known microwave ablation probes are at least similar to the oblong ablation zones (170) (Figure 13) produced by ablation probe systems (50) (those used with the probe tip (100c)). Microwave ablation (MAB) and radiofrequency ablation (RFA) are well-established methods for inducing tissue heating that leads to coagulative necrosis (cell death). However, MAB and RFA generate oblong-shaped ablation zones relative to the position of the ablation probe's insertion path. As a result, conventional medical ablation technology proved suboptimal for many tooth bud ablations, since the ablation zone created with conventional medical ablation systems does not destroy tooth bud tissue without also unnecessarily destroying adjacent non-tooth bud tissue. If an incorrectly shaped ablation zone is used, it is nearly impossible to deliver the correct amount of ablation media without unnecessarily destroying tooth bud tissue. For example, if the tooth buds are spherical and the ablation zone is oblong, too much tissue will be ablated (tissue outside the tooth buds will be ablated), damaging the surrounding tissue, or too little tissue will be ablated, potentially resulting in an unsuccessful ablation.In other words, unlike conventional medical ablation technology, the tooth bud ablation system described herein utilizes a patented shape-zone technology for a more optimized fit within the tooth buds. This system more selectively destroys the target tooth bud tissue while destroying a significantly smaller amount of non-target tissue. This greatly reduces the possibility of collateral tissue damage, thereby minimizing the risk of adverse side effects. Figures 14A to 14C and Figures 15A to 15C show representations of the heating patterns that give rise to the conformal ablation zones. Both the drawings in Figures 14A to 14C and the photographs in Figures 15A to 15C show a plurality of isotherms represented as a series of relatively annular lines (which can be thought of as nested rings) emanating from a relatively central region or point (an annular aperture (120) and / or an ablation center (124) bounded by the annular aperture (120)) on the tip axis (102). Each of these isotherms represents ten degrees Celsius (10 °C) and, starting from the highest temperature in the active heating zone (125), decreases outward by thermal conduction in the heating zone (126), to the outermost annular line representing fifty degrees Celsius (50 °C).In other words, an image with four nested ring lines (an example of which is shown in Figure 23B) would mean that the first (innermost) ring would represent eighty degrees Celsius (80°C), the second ring would represent seventy degrees Celsius (70°C), the third ring would represent sixty degrees Celsius (60°C), and the fourth (outermost) ring would represent fifty degrees Celsius (50°C). Since the exemplary temperature required for tooth ablation is sixty degrees Celsius (60°C), the shape of the ablation zone would be based on the penultimate ring (in the four-ring example, the third). The system could be adapted to use isotherms representing different temperatures (e.g., eight degrees Celsius (8°C) or twelve degrees Celsius (12°C)).Furthermore, the system could be adapted to alternative minimum temperatures needed for the ablation of different soft tissues that require higher or lower temperatures for ablation. Figures 16A to 16C show photographs comparing ablated tissue from a procedure performed using known medical ablation systems (Figures 16A to 16B) with the medical ablation system described herein (Figure 16C). Figure 16A illustrates the adverse impact of using conventional medical ablation at 2.45 GHz. The ablation zone in the soft tissue is highly irregular in the active heating zone (125), overheated at one end, and has an extremely oblong shape as it migrates asymmetrically upward along the ablation probe axis as it heats up. Figure 16B shows an ablation zone produced at a higher frequency. It has a teardrop shape that migrated asymmetrically out of the spherical shape of a tooth bud that occurred because the probe shaft got too hot and is also suboptimal for tooth bud ablation.Figure 16C shows a spherical ablation zone generated using the tooth outline ablation probe described herein. The shape of the ablation zone represents an optimal fit within the soft tissue of the tooth outlines and can be configured to be wider, spherical, or oblong along the insertion path of the microablation probe because the active heating zone (125) is predefined with thermal energy that is conducted out of the active heating zone (125) and into the thermal heating zone (126) in a controlled manner. II.A. Ablation probe: Figures 8 to 13 show exemplary microwave ablation probe tips (100) (which, unless otherwise specified, generically include the ablation probe tip (100a) in Figure 11, the ablation probe tip (100b) in Figure 12, and the ablation probe tip (100c) in Figure 13). These ablation probe tips are designed for the thermal heating of tissues. The thermal heating mechanism occurs in an active heating zone (ablation zone) due to the vibration of highly polar water molecules in the case of microwaves (MW) or the vibration of ions in water in the case of radiofrequency (RF).The structure shown and described of the ablation probe tips (100) conductively transfers excess heat in the target ablation zone out of the target ablation zone into the surrounding non-target tissue at temperatures below the threshold where tissue destruction will occur. The structure shown and described of the ablation probe tip (100) (including the near-field antenna (110), a coaxial cable with an annular aperture (120)) utilizes the emission of “near-field reactive” energy in the ablation zone regions and can therefore be considered a near-field antenna. (This can be thought of as a near-field reactive antenna.) The “near-field reactive” regions are approximately λ / 2π ~0.159 wavelengths or less in the antenna length of the ablation probe where the microwave energy does not propagate as a uniform wave (λ being the spatial period of a periodic wave, i.e., the distance over which the waveform repeats).As described below, near-field radiation regions are distinctly different from far-field radiation regions, where the microwave signal propagates far enough for the waveforms to propagate as more coherent waves in the far-field radiation regions. The shown and described structure of the ablation probe tip (100) preferably delivers non-resonant energy in a combined aperture / ablation zone dimension that is smaller than the wavelength of the frequency divided by 4 to minimize the production of thermal energy along the axis (102) of the probe tip. ML / E / ZuZZ / uU11 9 ablation (100). The optional insulating ring layer (118) can be a thermally conductive outer sheath that further minimizes the production of thermal energy along the tip of the ablation probe (100). Figures 8 to 10 show the shaft (102) of the ablation probe tip (100), which has an insertion end (104) (also called the insertion point or point of insertion) at the end of the shaft (102). The insertion end (104) may be sharp enough to self-insert. The ablation probe tip (100) has a central coaxial antenna (110) (which can be considered as a coaxial cable with an annular aperture (120)). The central coaxial antenna (110) preferably includes an inner conductor (112), an annular dielectric insulating layer (114) (or other waveguide), an outer annular conductor (116), and an optional annular insulating layer (118). Toward the end of the coaxial antenna (110) (near the insertion end (104)) is an annular aperture (120) (which can be considered as an annular window).Between the aperture (120) and the insertion end (104) of the coaxial antenna (110), an optional antenna end load can be placed to increase the antenna's capacitive properties. This shortens the length of the antenna's center wire, thereby reducing the focal region (concentrating the overall power density) and increasing the power load (power density) in the ablation zone. This will be discussed in more detail in connection with power load control (section VI). Around the coaxial antenna (110) on the axis (102) (and separated from the insertion end (104)) is an annular heat transfer layer (130) (also called the thermal conductive layer (130)), and an annular tip cover (132) is located at the insertion end (104). The annular tip cover (132) covers and surrounds the coaxial antenna end (110), the annular aperture (120) and the optional antenna end load (122).Furthermore, the annular surface of the annular tip cover (132) furthest from the insertion end (104) abuts in an annular manner with the annular surface of the thermally conductive layer (130) closest to the insertion end (104). The central coaxial antenna (110) preferably includes an inner conductor (112) annulus-surrounded by an annular dielectric insulating layer (114) (e.g., polytetrafluoroethylene (PTFE), air, or other known dielectrics), which is in turn surrounded by an annular outer conductor (116). The inner conductor (112) may be copper, copper-clad steel, silver-plated steel, or other conductive materials. The annular dielectric insulating layer (114) may be PTFE, air, or other known dielectrics that help form a waveguide between the central conductor and the annular outer conductor. The annular outer conductor (116) may be a metallic shield, such as a solid or woven shield of copper, aluminum, or other known metals. The coaxial antenna (110) can be purchased, prefabricated, or a combination of both (e.g., purchased without an aperture and adding the aperture later, or purchased without an insulating layer and adding the insulating layer later). The antenna can be a design with a capacitive end load (as shown), a dipole antenna without a capacitive load, or an antenna with another method of loading the antenna end. Although an antenna design with an end load to increase capacitive coupling and shorten the antenna length is shown, a dipole antenna without an end load or another method of capacitively loading the antenna end can be used to lengthen or shorten the antenna. The ablation probe tip (100) may also include an optional insulating ring layer (118) that provides thermal and electrical insulation between the outer ring surface of the outer conductor (116) and the inner ring surface of the heat transfer layer (130). Although shown with the optional insulating ring layer (118), alternative preferred ablation probe tips may omit the insulating ring layer. The optional insulating ring layer (118) may be part of a coaxial antenna (110) (e.g., a prefabricated or purchased coaxial antenna). Alternatively, the optional insulating ring layer (118) may be added to a coaxial antenna (110) (e.g., a prefabricated or purchased coaxial antenna) that does not have its own insulating layer.The insulating ring layer (118) may be made of materials including, but not limited to, plastics such as polymethacrylate, polysulfone or polyetherimide or other materials such as zirconium dioxide or lithium disilicate ceramic capable of providing electrical insulation. Toward the end of the coaxial antenna (110) (near the insertion end (104)) is an annular aperture (120) shaped like a 360-degree slot. In other words, the annular aperture (120) is a portion of the coaxial antenna (110) where the annular dielectric insulating layer (114) is free of the outer annular conductor (116). Put another way, the annular aperture (120) is where the outer annular conductor (116) has been removed (or was never present) in an annular ring around the exposed annular ring of the dielectric insulating layer (114). The ablation center (124) (the focal point or region from which the ablation medium radiates) is located within the inner conductor (112) in the annular aperture (120) (from which the ablation medium emanates). This is discussed in the section on central ablation control (Section III).), the ablation zones (150, 160, 170) remain centered around the annular opening (120) and the ablation center (124) and do not migrate symmetrically upwards from the axis (102). When the ablation probe tip (100) is mounted, the annular tip cover (132) covers the annular opening (120). As stated herein, the optional antenna end load (122) is placed between the annular aperture (120) and the insertion end (104) of the coaxial antenna (110) and acts to enhance the antenna's capacitive properties. The optional antenna end load (122) is preferably at least substantially perpendicular to and adjacent to the inner conductor end (112). The optional antenna end load (122) functions as a capacitive concentrator such that the ablation media strike the antenna end load (122) and are radiated toward the target tissue from a shorter effective base of the antenna.The exemplary microwave ablation probe tip (100) has a shaft design with an annular heat transfer layer (130) that at least partially surrounds the central coaxial antenna (110). The heat transfer layer (130) is preferably the outermost annular layer of at least the portion of the shaft (102) that it covers. As will be discussed in relation to Figures 11 to 13, the heat transfer layer (130) is positioned to create an oblate ablation zone (150), a spherical ablation zone (160), or an oblong ablation zone (170) along the shaft (102) of the ablation probe tip (100).The positioning of the heat transfer layer (130) may be predetermined, or the heat transfer layer (130) may be positionable (e.g., movable, sliding, or otherwise attachable to different positions) along the axis (102), the shape of the ablation zones (150, 160, 170) being determined by the position of the heat transfer layer (130). In use, the heat transfer layer (130) extends partially within the ablation zone, while part of it remains outside. The heat transfer layer (130) is preferably made of a material that has high thermal conductivity and is electrically conductive. In other words, the heat transfer layer (130) is preferably a layer of high thermal conductivity. (Preferably, the heat transfer layer (130) is both microwave-transmitting and thermally non-conductive.)Exemplary materials include, but are not limited to, silver (Ag), aluminum (Al), copper (Cu), stainless steel (Ss), titanium (Ti), or any other known or yet-to-be-discovered material that has high thermal conductivity and is electrically conductive. For example, silver has higher conductivity than copper, aluminum has high conductivity (but lower conductivity than copper), stainless steel has poor thermal conductivity, and titanium has worse thermal conductivity than stainless steel. The different thermal conductivity properties of various materials allow for the construction of devices with varying thermal conductivity properties, which can be used to create a variety of ablation probe tips for use in different applications. This is discussed in the section on controlling the temperature of the ablation zone (Section IV).), the preferred heat transfer layers (130) passively cool the ablation probe tip (100) minimizing the production of thermal energy along the portions of the ablation probe tip (100) substantially adjacent to or close to the heat transfer layer (130). The tip of the sample microwave ablation probe (100) has a design of ML / E / ZuZZ / uU11y tip with a tip cover (132) at the insertion end (104). The tip cover 132 is preferably made of a material or substrate that has both high radiotransparency (meaning it is highly radiotransparent or has low microwave absorption rates) and low thermal conductivity (meaning it is highly insulating or has low thermal conduction rates) while also being electrically non-conductive. Suitable exemplary materials for this purpose include, but are not limited to, plastics such as polysulfone, polyetherimide, and polymethacrylate, but may also include ceramic substrates such as zirconium dioxide and lithium disilicate.Ablation probes with this tip design have the properties of allowing microwave energy to escape preferentially (high radiotransparency), blocking heat from returning to the inside of the ablation probe (low thermal conductivity), and high electrical insulation. II.B. Ablation zones: Figures 8 to 10 show the basic components of the ablation probe tip (100) and Figures 11 to 13 show the specific ablation probe tips (100a, 100b, 100c) that create the three ablation zones differently (150, 160, 170). Although Figure 9 shows three different ablation zones (150, 160, 170), it incorrectly shows a single aperture displacement. Figures 11 to 13 correctly show the different aperture displacements ((152, 162, 172)) with respect to the outer annular conductor (116) that would be necessary to create the respective ablation zones (150, 160, 170). Similarly, Figure 10 shows an exemplary energy flow from the ablation probe tip (100a) of Figure 11, but the flows would be similar for the ablation probe tips (100b) and (100c) of Figures 12 and 13. Figure 10 shows an exemplary energy flow from an exemplary ablation probe tip (100) that can be described in eight flow steps (FS1–FS8). Most of the flow step reference numbers point to arrows indicating the direction of energy flow. Although described as steps to represent flow, many of the steps actually occur continuously and / or simultaneously. The probe tip (100), as an example, uses microwave energy as the ablation medium (62). FS1: The ablation means (62) provided by the ablation source (60) are inserted or injected into the central coaxial antenna (110) and are moved through the waveguide (e.g., the dielectric insulating layer (114)) between the inner conductor (112) and the annular outer conductor (116). ML / E / ZuZz / u U11» FS2: The ablation medium (62) then exits through the annular aperture (120) near the antenna end load (122). The exit of the ablation medium carries energy that acts on the reactive near-field region of the antenna with an effective antenna length of approximately λ / 2π (-0.159 wavelength) or less. FS3: The ablation media (62) begins to radiate outward as near-field radiation from the annular aperture (120) through an annular tip cover (132). The length of the annular aperture determines the effective antenna length and the effective power load (power density), with a larger annular aperture resulting in a lower effective power density going to the target tissue. As stated herein, the annular tip cover (132) has the dual properties of being highly radiotransparent to the outward-flowing MW or RF energy, while also being highly insulating so that the ablation probe tip (100) does not conduct thermal energy inward when the ablation media (62) passes through it. FS4: After traveling through the highly radiotransparent annular tip cover (132), the ablation media (62) are subsequently absorbed into the living tissue (91) (which may be a dental (92) or surrounding tissue) around the annular tip cover (132) in what will become the active heating zone (125), which begins to rapidly heat the tissue (91) as the MW or RF energy is converted into thermal energy. FS5: As the tissue (91) around the annular tip cover (132) increases its temperature sufficiently to form the ablation zone, the low thermal conductivity / high insulating properties of the annular tip cover (132) preferentially block the thermal energy from the tissue so that it is not conducted back towards the antenna structure of the ablation probe tip (100) and migrates upwards through the central coaxial antenna (110) and the outer annular conductor (116). FS6: In addition to the dual properties of the annular tip cover (132), the shaft (102) of the ablation probe tip (100) also contains an electrically and thermally insulated annular heat transfer layer (130) that blocks the transmission of the ablation media (62) upwards along the shaft (102), while allowing thermal energy from the active ablation zone to be preferentially conducted upwards through the annular heat transfer layer (130) from the ablation zone of the soft tissue (91) that is being heated. FS7: The annular heat transfer layer (130) is turned off by transferring its thermal energy to the soft tissue (91) in contact that is not being heated directly by the ablation means (62) because the annular heat transfer layer (130) has blocked the ablation means (62) from migrating upwards along the shaft (102). FS8: The cooling mechanism of the annular heat transfer layer ML / IZ / ZZZZ / υΊ U11» (130) by the adjacent soft tissue (91) is not only produced through its high thermal mass due to the high water content, but the soft tissues (91) are perfused by the moving blood, which means that heat is carried away from the annular heat transfer layer (130) and out of the surrounding soft tissue (91). The aperture offsets shown ((152, 162, 172)) in Figures 11a-13 create the different shapes of the ablation zone (150, 160, 170). More specifically, the length-to-width ratio (aspect ratio) of the ablation zone increases with increasing aperture offset, resulting in a more oblong shape. The aperture offsets ((152, 162, 172)) can be described as the distances (setbacks) between the annular aperture (120) (and / or the ablation center (124)) and the annular heat transfer layer (130). For consistency, the aperture displacements (152, 162, 172) shown and described herein are the distance between the center of the annular aperture (120) (shown as the effective ablation center (124) and also referred to as the center of the annular aperture (124)) and the annular edge of the annular heat transfer layer (130) nearest to the annular aperture (120).Since the ablation center (120) is stationary (does not migrate), as discussed in the central ablation control section (section III), the ablation center (124) and the center of the annular aperture (124) remain the same. It should be noted that, although the distances would be different, the aperture displacements could be measured from alternative reference points (e.g., the annular edge of the outer annular conductor (116) closest to the annular aperture (120)). The examples in Figures 11–13 are based on exemplary ablation probe tips with apertures ranging from 1.00 mm to 1.50 mm. The exemplary frequency used was 12 GHz, and the exemplary power used was 6.6 W. (Other frequencies, including 18 GHz, could produce shaped ablation zones.) The aperture deviation ranged from 0.0 mm to 3.0 mm. Measurements were taken at 20-second intervals. Each probe was frequency-tuned in water to obtain the minimum reflected power reading before each ablation. (Figure 17 shows the results of an exemplary probe experiment relating ablation zone roundness to the thermal conductivity of the outer annular conductor (116) and the effective aperture size (120).) Figure 11 shows the ablation zone (150) with an oblate shape. The aperture offset (152) is the shortest of the aperture offsets (152, 162, 172) and creates the oblate ablation zone (150). As an example, for a near-field probe tip, the aperture offset can be less than 1.0 mm. The ablation zone (150) has an aspect ratio greater than 1.0 (aspect ratio > 1.0). Figures 14A and 15A show isotherms of the ablation zone with an exemplary oblate shape. Figure 12 shows a spherical ablation zone (160). The aperture offset (162) has a length between the aperture offset (152) and the aperture offset (172) and creates the spherical ablation zone (160). As an example, for a near-field probe tip, the aperture offset might be approximately 2.0 mm (or at least between 1.0 mm and 4.0 mm). The ablation zone (160) has an aspect ratio of 1.0 (aspect ratio = 1.0). Figures 14B and 15B show isotherms of the ablation zone with an exemplary spherical shape. Figure 13 shows an oblong ablation zone (170). The aperture offset (172) is the longest of the aperture offsets (152, 162, 172) and creates the oblong ablation zone (170). For example, for a near-field probe tip, the aperture offset can be greater than 4.0 mm. The ablation zone (170) has an aspect ratio less than 1.0 (aspect ratio < 1.0). Figures 14C and 15C show the isotherms of the ablation zone with an exemplary oblong shape. As will be discussed in the calibration section and in conjunction with CT-guided ablation volume and / or diameter control (section V.), the ablation zone shape can be calibrated. III. Ablation center control Conventional microwave ablation (MAA) and radiofrequency ablation (RFA) technologies proved suboptimal for tooth outline ablation for several reasons. Medical ablation systems were reviewed and rejected because they demonstrated substantial asymmetric migration of the ablation zone upward from the ablation probe axes during the procedure. The outer margin of the soft tissue ablation zone migrates asymmetrically upward from the probe tip axis as the probe heats up. Furthermore, the effective center of ablation also migrates upward from the tip axis as the ablation probe heats up. This asymmetric migration of the ablation zone makes predetermining or planning a medical ablation procedure extremely difficult for the operator and poses a significant risk of damaging tissue outside the planned ablation zone. As previously stated, the ablation center (124) is located in the center of the inner conductor (112) and is annulus-surrounded by the annular aperture (120). The ablation center (124) is also the effective center of the ablation zones (150, 160, 170). The ablation center (124) is also referred to as the “center of the annular aperture (124).” The microablation technology described herein has been designed to eliminate asymmetric upward migration of the ablation zone from the axis of the ablation probe tip during MLE / E / ZUZZ / Ul Ul 1U the ablation procedure. Elimination of migration can be considered as fixing the ablation center (124) in place relative to the ablation center (124), the annular opening (120), and / or the ablation probe tip (100). In other words, the preferred ablation probe tips (100) described herein have stationary (also called fixed) ablation zones (150, 160, 170) in the sense that they remain centered on the annular opening (120) and the ablation center (124). This is shown in Figure 19. The outer margins of the ablation zones (150, 160, 170) do not migrate asymmetrically upwards (towards the handpiece (52)) from the probe tip axis (102) as the ablation probe tip (100) is heated.Furthermore, the effective ablation center (124) within the center of the tissue does not migrate upwards (towards the handpiece (52)) along the probe tip axis (102) as the ablation (100) is heated. The outer annular heat transfer layer (130) of the microablation probe, in combination with the use of a near-field antenna, keeps the center of the ablation zone immobile as the ablation zone expands symmetrically outwards, as shown in Figure 19. As discussed in relation to Figure 10 (FS6), the outer annular heat transfer layer (130) has two properties: (1) it blocks the transmission of the ablation media (62) so that they do not migrate upwards along the shaft (102) and (2) it simultaneously allows thermal energy from the active ablation zone to be preferentially conducted upwards through the annular heat transfer layer (130) from the ablation zone of the soft tissue (91) that is being heated. Once the microablation probe tip (100) is positioned within the target tissue (92), the ablation procedure is activated by the operator using the ablation source (60). The ablation media (62) flows through the ablation probe system (50) and radiates outward from the ablation center (124). The energy / heat radiating outward from the ablation center (124) forms the ablation zones (150, 160, 170). While energy is radiated outwards from the center, the ablation center (124) and the ablation zones (150, 160, 170) remain stationary relative to the ablation center (124) in the sense that the ablation zones (150, 160, 170) remain centered around the ablation center (124) and the outer margins of the ablation zones (150, 160, 170) do not migrate upwards from the axis of the probe tip (102) as the ablation probe tip (100) is heated.Instead, the properties of the near-field antenna (110) (the central coaxial antenna (110)) and / or the properties of the outer annular heat transfer layer (130) prevent upward migration (away from the insertion end (104)) relative to the axis (102). This is true regardless of whether the shape of the ablation zone is oblate, spherical, or oblong. No competing technology is known to have this unique ability to keep the ablation zone in a fixed position throughout the ablation procedure, and therefore no other medical ablation technology has this degree of centering capability. IV. Temperature control of the ablation zone Another aspect of the tooth bud ablation process is temperature control in the ablation zone. The maximum temperature is limited throughout the procedure to prevent tissue charring. A comparison between overheated and properly heated tissue can be seen by comparing Figures 20A and 20B. Figure 20A shows the superheated tissue, which can be seen as generated steam (shown as the wavy inner ring) in the central region of the active heating zone (125) around the probe tip. This would occur when the maximum temperature exceeds one hundred degrees Celsius (100 °C). Steam generation dehydrates tissue, which can lead to charring and abnormal healing, including the formation of residual scars. In other words, if the maximum temperature is not controlled, unpredictable healing can occur, potentially resulting in scarring. When scarring occurs, the soft tissue may not heal normally. Figure 20B shows adequately heated tissue where a temperature-controlled ablation process does not exceed ninety degrees Celsius (90°C). When peak temperatures do not exceed one hundred degrees Celsius (100°C), there is little chance of tissue dehydration during ablation or of abnormal scarring occurring after the operation, detectable radiographically. Based on multiple animal studies, when peak temperatures are limited to ninety degrees Celsius (90°C), the bone fills in within a short period, and tooth buds are no longer detectable on radiographs in just four (4) weeks. Therefore, it is highly advantageous to maintain peak temperatures at ninety degrees Celsius (90°C) or lower. There are two main types of temperature control that can be used in the ablation probe system: passive cooling and active cooling. Temperature is also affected by power load control, as explained in the Power Load section (Section VI). ML / E / ZuZz / u U11» IV.A. Passive cooling: The preferred ablation probe tips (100) (including the probe tip shaft (102)) described herein include passive cooling (passive ablation zone temperature control). For passive cooling, the heat transfer layers (130) passively cool the ablation probe tip (100) by minimizing thermal energy production along the portions of the ablation probe tip (100) substantially adjacent to or near the heat transfer layer (130). The passive cooling of the preferred ablation probe tips (100) thus keeps the probe tip shafts (102) relatively cool. The ablation probe tips (100) described herein utilize the thermal properties of the adjacent living tissue (91) (the specific thermal mass of the soft tissue (91) and the active blood perfusion of the soft tissue (91)) to cool the ablation probe tip (100) and help shape the ablation zones (150, 160, 170). This feature may be referred to as tissue cooling. Tissue cooling is shown in Figure 10 (flow steps FS7 and FS8), which is discussed herein. IV.B. Active cooling: It should be noted that many known microwave ablation probes require some form of active cooling (e.g., active pumping of coolant (such as water) or gas (such as CO2) along the probe tip axis), otherwise the shaft overheats and tissue charring occurs along the axis with local temperatures sometimes exceeding 300 °C. However, the preferred ablation probe tips (100) described herein, which create ablation zones less than 25.0 mm in diameter, may not require active cooling to prevent the probe tip axis (102) from becoming so hot that tissue (91) is ablated along the probe tip axis (102). Some preferred ablation probe tips (100) described herein may also include optional active cooling for the ablation zones. In active control of the ablation zone temperature, feedback from the ablation source (60) and / or the ablation probe tip (100) (which may have at least one sensor (108) along the axis (102) for monitoring, for example, temperature) may be provided to the user (or to electronic or digital monitoring systems that may be implemented by software) using an output mechanism (68) such as a video display or an audio display (speaker). For the ablation probe systems (50) described herein, the optional exemplary active cooling (54) (which includes cooling materials such as Liquid coolant (such as water) or gas (such as CO2) can be supplied through the handpiece (52) and / or directly to the tip of the ablation probe (100). Using the probe (100) in Figure 8, the coolant (54) can flow between the outer annular conductor (116) and the heat transfer layer (130). If an optional insulating annular layer (118) is present, the coolant (54) could flow either into or outside the optional insulating annular layer (118). Alternatively, the cooling (54) could travel through channels and openings (not shown) incorporated in or through the heat transfer layer (130). There are four variables that can be controlled and that are related, at least tangentially, to temperature control (active cooling): power / temperature, frequency / penetration, time / size, and shape / roundness. • Power / Temperature: The power is kept low to prevent the maximum temperature from exceeding ninety degrees Celsius (90 °C). • Frequency / Penetration: The frequency is selected to penetrate deeper into the tissue (i.e., there is less need for conduction and higher temperature). • Time / Size: The size of the ablation zone can be determined by the duration of the ablation process (typically 20 to 40 seconds). In addition to controlling the total ablation time, modulating the energy on and off in a controlled manner (pulse width modulation) is part of the time control. • Shape / Roundness: The shape / roundness of the ablation zones (150, 160, 170) is determined by the design of the ablation probe tip (100), including, for example, the size of the aperture offset (e.g., aperture offsets (152, 162, 172)). However, these variables can be intertwined. For example, a large ablation zone (time / size) may take longer to heat up (power / temperature) than a small ablation zone. Pulse-width modulation of time / energy can also improve the degree to which an ablation zone becomes more oblate. The combination of variables is generally controlled by the ablation source (60), which can be controlled manually (regularly) and / or automatically (intelligently). At least an initial set of parameters for the variables may be part of a prescription (in a surgical unit) that is entered (programmed) into the ablation source (60). The combination of variables is based on an empirical map (developed on the basis of extensive testing) and / or on the use of at least one sensor that provides information. An empirical mapping of the ablation process shows that the maximum temperature and temperature gradients are based on the total energy / power and frequency. ML / E / ZuZz / u U11» Empirical tests can be used, for example, to determine the maximum energy input (power) as a function of time. After conducting thorough tests and plotting the maximum temperatures, overheating can be prevented by controlling the variables (e.g., by controlling the energy input). Alternatively, or in conjunction with empirical testing, at least one external temperature sensor can be placed on the surface of the ablation probe (100). Precise control of the power supply with feedback from at least one sensor can be a key component for temperature control. Several fiber optic-based temperature sensors exist that do not interfere with microwave energy emission, including, for example, fiber optic temperature sensor solutions from OSENSA Innovations (Burnaby, BC, Canada). Temperature information from at least one fiber optic sensor can be provided to (coupled to) the ablation source (60) to adjust and maintain the desired temperature. Feedback can be provided as input to the ablation source (60). Feedback can be provided to the user via an output mechanism (68), such as a video display or an audio display (speaker). The user can then manually adjust the parameters (64) and the treatment time (66) (including stopping the treatment) of the ablation source (60). Feedback can also (or alternatively) be provided directly to an output mechanism (68) (e.g., a smart generator) (or to the electronic or digital monitoring systems associated with it, which may be implemented by the software associated with the ablation source (60)) that automatically adjusts the parameter settings (64) and the treatment time settings (66). V. Control of the volume and / or diameter of the guided ablation Controlling the ablation volume is another aspect that can be crucial for the success of the procedure. To achieve this, the ablation source (60) (e.g., an intelligent microablation generator) precisely delivers the prescribed ablation zone volumes. These volumes are determined preoperatively using volume scan images and provided as a prescription, along with parameters for relevant variables (e.g., time and power). The ablation source (60) primarily controls the energy delivery (e.g., speed and time) to generate the prescribed ablation zone volume within the bone crypt of the tooth outlines. This allows the system to provide ablation zone margins of + / - 0.5 mm (within statistical limitations) for the prescribed ablation. This technology has the unique ability to ML / IZ / ZZZZ / υUII and be able to predetermine and supply the final diameter and ablation volume with this degree of accuracy. Figure 21 shows four images: one original image (top left) and three marked images (top right, bottom left, and bottom right). The top left image is of the selected dental sketch. The three marked drawings each include a dashed circle representing the dental sketches. They also include a solid circle with arrows radiating from the center to the inner perimeter, representing the ablation zone. The top right image shows the dental sketches under-ablated because the ablation zone is significantly smaller than the dental sketches. The bottom left image shows the dental sketches over-ablated because the ablation zone is larger than the dental sketches.The lower right image shows the dental outlines correctly ablated because the ablation zone is relatively tight (the annular distance between the ablation zone within the dental outlines may be slightly exaggerated) to the dental outlines. Using the prescription of the procedure guided by the volume scanner, the ablation medium (62) (e.g., the smart microwave generator) controls the energy delivery (both speed and time) to generate the prescribed ablation zone volume within the bone crypt of the tooth outlines once the ablation probe is in the correct position. Extensive experiments were conducted on both tooth outlines (ex vivo) and pig loin to determine the estimated duration required for varying ablation diameters. The results of these experiments were analyzed, and the graph in Figure 22 and the table below present some of the findings. In the graph in Figure 22, the solid line shows the estimated ablation diameters on tooth outlines for various durations. The dashed line above the solid line shows the diameter estimates for ablations on pig loin. The graph below adds the additional variable of a specific diameter representing the diameter of the bone crypt, along with a correlation between the ablation duration and the estimated diameter of the ablation zone. ivia / t / zuzz / uiu 11 and Ablation Duration Table for In Vivo Pig Ablations Largest Bone Crypt Diameter Measured on CT Image (mm) Ablation Duration (seconds) Estimated Final Ablation Zone Diameter (mm) 4 0 to 4.5 20 6.2 4 6 to 5.0 25 6.8 5 1 to 5.5 30 7.2 5 6 to 6.0 40 8 0 6 1 to 6.5 45 8.4 6 6 to 7.0 55 9 0 7 1 to 7.5 65 9.6 7 6 to 8.0 75 10.1 8 1 to 8.5 85 10.6 8 6 to 9.0 95 11.1 9 1 to 9.5 110 11.7 ML / E / ZUZZ / Ul Ul 1y VI. Power Load Control As explained herein, the length of the annular aperture (and the size of the focal region within it) determines the effective length of the antenna and / or the effective power load (also referred to as "power density" and "power load density"). Compared to larger annular apertures, smaller annular apertures produce relatively higher effective power densities in the active heating zone (125) of the target tissue. Conversely, compared to smaller annular apertures, larger annular apertures produce relatively lower effective power densities in the active heating zone (125) of the target tissue. Since the size of the annular apertures can be controlled and / or predetermined, the power load densities can also be controlled and / or predetermined (a predetermined power load density). As stated herein, the length of the annular aperture (and the size of the focal region within it) determines the maximum effective temperatures in the active heating zone (125). Compared to larger annular apertures, smaller annular apertures produce relatively higher maximum effective temperatures in the active heating zone (125). Conversely, compared to smaller annular apertures, larger annular apertures produce relatively lower maximum effective temperatures in the active heating zone (125). Since the size of the annular apertures can be controlled and / or predetermined, the peak temperatures in the active heating zone (125) can be controlled and / or predetermined to be high peak temperatures, medium peak temperatures, low peak temperatures, or a predetermined peak temperature.The maximum temperatures are relative to other ablation probe tips and systems that have the same parameters and / or variables. As discussed in the ablation probe section (Section II.A.) of the ablation zone shaping control section (Section II.), a final antenna loading (122) near the aperture (120) of the coaxial antenna (110) increases the capacitive properties of the antenna (110) to shorten the length of the antenna's center wire. This makes the focal region (124) smaller (concentrating the energy density) and increases the power loading (power density) in the ablation zone (150, 160, 170) (shown in Figures 23A to 23C as ablation zones (160a, 160b, 160c), which are variations of the spherical ablation zone (160)). There are other ways to change (increase / decrease) the size of the focal region (124), including, but not limited to, antenna designs using pig-tail catheters and other known techniques and technologies used to add end loads to increase the power load of antennas. Figures 23A to 23C and Figures 24A to 24C are graphic and photographic images showing the effect of the focal region size (the ablation center (124) bounded by the annular aperture (120) (shown as (120a, 120b, 120c) in Figures 23A to 23C) on the creation of the ablation zones (150, 160, 170) (although only the approximately spherical ablation zone (160) is shown). Apart from the size of the annular aperture (120), the variables (e.g., time, power, etc.) in the experiments documented by these photographs remained constant. The rings in these photographs are like the rings in Figures 15A to 15C in that the isotherms (annular lines) surrounding the focal region each represent ten degrees Celsius (10 °C). and the outermost isotherm (ring line) represents fifty degrees Celsius (50 °C). The exemplary isotherms are labeled in Figures 23A to 23C. The heating rate (temperature change / time change) that increases as the annular aperture becomes smaller can be mathematically expressed. Power density can be considered as the amount of power (rate of energy transfer over time) per unit volume. In this equation (and only as an example), the amount of power is expressed in watts (W) and the unit of volume is expressed in cubic millimeters (mm³). If 5.0 W of microwave energy is applied to a probe tip with an annular aperture 1.0 mm long, the power density would be approximately 5.0 W / mm³. If 5.0 W of microwave energy is applied to a probe tip with an annular aperture 4.0 mm long, the power density will be approximately 1.25 W / mm³. The ablation probe shown in Figure 24A has a small focal region MA / IZ / ZU¿Z / U1 Ul 1U creating a high power load density in the ablation zone (160a). More specifically, the focal region is an annular aperture (120a) of 0.8 mm (length along the probe axis). If 5.0 W of microwave energy were applied to this probe tip, the power density would be approximately 6.25 W / mm³ when the microwave energy begins to penetrate the tissue. The maximum internal temperature of the ablation zone in the active heating zone (125) is ninety degrees Celsius (90 °C). Figure 23A shows a similar probe tip (100) creating a spherical ablation zone (160a) (although other shapes could be created using probes with shorter or longer aperture offsets) with an active heating zone (125) and a thermal heating zone (126).The short annular aperture (120a) limits a short / small focal region (124) which in turn gives rise to a short / small active heating zone that creates a high power load (represented by the relative proximity (narrow dispersion) between the isotherms in the thermal heating zone (126) of the ablation zone (160a)). The ablation probe shown in Figure 24B has a medium focal region that creates a medium power load density in the ablation zone (160b). More specifically, the focal region is an annular aperture (120b) of 1.5 mm (length along the probe axis). If 2.4 W of microwave energy is applied to this probe tip, the power density would be approximately 3.3 W / mm³ when the microwave energy begins to enter the tissue. The maximum internal temperature of the ablation zone in the active heating zone (125) is 80°C. Figure 23B shows a similar probe tip (100) that creates a spherical ablation zone (160b) (although other shapes could be created using probes with shorter or longer aperture offsets) with an active heating zone (125) and a thermal heating zone (126).The mean annular aperture (120b) limits a mean focal region (124) which in turn gives rise to a medium length / size active heating zone that creates a medium power load (represented by the intermediate propagation isotherms in the thermal heating zone (126) of the ablation zone (160b)). The ablation probe shown in Figure 24C has a large focal region that creates a low power load density in the ablation zone (160c). More specifically, the focal region is an annular aperture (120c) of 4.0 mm (length along the probe axis). If 2.4 W of microwave energy is applied to this probe tip, the power density would be approximately 1.25 W / mm³ when the microwave energy begins to enter the tissue. The maximum internal temperature of the ablation zone in the active heating zone (125) is seventy degrees Celsius (70 °C). Figure 23C shows a similar probe tip (100) creating a spherical ablation zone (160c) (although other shapes could be created using probes with longer or larger aperture deviations) with an active heating zone (125) and a thermal heating zone (126).The long annular aperture (120c) delimits a long / large focal region (124) which, in turn, gives rise to a long / large active heating zone that creates a low power load (represented by the relatively large distance (wide dispersion) between isotherms in the thermal heating zone (126) of the ablation zone (160)c). Power density is one of the capabilities of an ablation probe tip (100) that would be relevant for calculations performed, for example, by software. Selecting an ablation probe tip (100) with an annular aperture (120) of a known or predetermined length will produce an ablation zone (150, 160, 170) with a known or predetermined power load. The ablation probe tip (100) with the predetermined annular aperture (120) may be included in a surgical kit, or the prescription may specify the ablation probe tip (100) with the predetermined annular aperture (120) to be used in the procedure. For clarity, it should be noted that power density is at least substantially independent of the shape of the ablation zone (150, 160, 170). While power density is related to the size of the annular aperture (120), the shape of the ablation zone (150, 160, 170) is related to aperture displacements (152, 162, 172). Calibration: Ablation probe systems are preferably calibrated (50). This can be achieved by performing a plurality of ablations (e.g., 150 ablations on dental outline tissue from freshly harvested jaws and maxillae of slaughtered animals) and using the results to establish a “calibration curve” based on the resulting ablation of the tissue. A volumetric image of the target tissue is taken. This image can be used to determine, for example, the volume / diameter of the ablation zone, the shape of the ablation zone, and / or the position of the ablation zone. Once the diameter of the bony crypt of each tooth outline has been measured, an “optimal” ablation zone can be created, for example, by selecting an ablation probe tip (100) and system settings based on the actual ablation volume properties of an ablation probe system. In other words, a probe with a predetermined three-dimensional ablation profile is used. The size and shape of the ablation probe tip (100) are also relevant, as they would be related to the positioning provided by the custom surgical stent (80). Finding the “best fit” would preferably involve determining that the volume / diameter of the ablation zone fits the tooth outlines. ML / E / ZuZZ / u U11 9 individual. Furthermore, finding the “best fit” would preferably include determining that the shape of the ablation zone conforms to the individual tooth outlines. In other words, the shape of the ablation zone is preferably controlled to fit within the tooth outlines. (For example, if the shape of the tooth outlines is oblong, then an oblong ablation zone is produced.) Adjustment of size and shape can be achieved, for example, by selecting the ablation probe tip (100) with the appropriate annular opening (120) to create the appropriate ablation zones (150, 160, 170). Another method for altering or controlling the shape is by using pulse-width modulation of the energy output from the probe.By properly positioning the ablation probe tip (100) using the procedures described in Therapeutic Properties of Tooth Outlines and in this document, the ablation zones are clearly centered circumferentially around the tooth outlines and greatly reduce the incidence of any adjacent non-target tissue (e.g., nerves, teeth, etc.) being damaged. The area of ​​the ablation zones can be calculated using the following example equation or other known methods of calculating areas (which may be more detailed and / or provide more accurate results): Area = average length * average width * pi The roundness of the ablation zones can be calculated using the following example equation or other known methods of calculating roundness (which may be more detailed and / or provide more accurate results): Roundness = average width / average length Other methods may be used to determine the area and roundness of the ablation zone, including, but not limited to, direct observation, measurement, and other known or yet-to-be-discovered empirical means of determining the area and roundness of the ablation zone. Illustrative use: The prophylactic prevention of third molar formation using the methods, systems, and procedures described herein, and the therapeutic properties of tooth bud ablation, offers many advantages. Earlier intervention is safer due to the anatomy (tooth buds are separated by 5 to 10 mm from the mandibular canal), the development of the tooth (the crown of the adjacent first and / or second molars (95) is generally well-developed), and improved healing (smaller surgical incisions reduce healing problems after the operation). With the devices, methods / procedures and systems described herein for inducing dental agenesis, the clinical objective is predictable efficacy in inducing dental agenesis with zero long-term adverse side effects. The devices, methods / procedures, and systems described herein can be used with the devices (custom surgical stents (80), virtual stents (82', 86', 88j, and / or surgical kits), methods / procedures, and systems described in the therapeutic properties of tooth outline ablation. For example, probes can be used with custom surgical stents (80) or virtual stents (82', 86', 88j) for accurate placement. A surgical kit (comprising an ablation probe system (50), a custom surgical stent (80), and ablation energy dose tolerances) is configured to maintain statistically consistent positioning control of the total ablation zone within + / - 0.5 mm of each tooth outline. The following exemplary steps can be used for dental agenesis (although the order may vary, e.g., the handpiece (52) may be connected to the ablation source (60) after the patient is seated): Routine studies from 6 to 14 years: Routine studies to determine the presence of tooth bud formation (92) (e.g., third molar buds) in two-year increments between 6 and 14 years of age, due to the wide age range that reflects the degree of variability in tooth bud formation. The study can be carried out using scanning techniques such as low-dose digital panoramic imaging techniques (which are common at least for most pediatric dentists and most general dentists) or even newer technologies such as ultrasound. Diagnosis and Volume Scanning: Once the presence of tooth outlines has been diagnosed during the study, a preoperative imaging step is performed to determine the three-dimensional location and volume of each tooth outline (92). This imaging can be practically carried out using, for example, three-dimensional CBCT dental volume scans with a voxel resolution of 0.4 mm or higher. The result is a three-dimensional digital volume scan. Preoperative Impressions: A dental impression (conventional physical or digital) of the teeth and soft tissue (gums) is obtained in at least the quadrant of interest. This impression captures the surface of the gingival tissue and the details of the teeth. The erupted first and / or second molars (95) and / or primary dentition are used to physically stabilize the surgical stent(s) (80). The creation of digital impressions is described in more detail in the section on therapeutic ablation of tooth outlines. Prescription of services: In a preferred method, a dentist can electronically complete and sign an online prescription form. The electronically signed prescription is preferably completed with the upload of a digital image. ML / E / ZuZZ / u U11» three-dimensional (for example, the CBCT digital image) and at least one dental impression. Ablation probe tip (100): The ablation probe tip (100) shall have a defined or known ablation zone (150, 160, 170). The ablation probe tip (100) shall have a defined or known penetration depth. The ablation probe tip (100) is preferentially self-inserting through the gingival tissue (94) into the tooth buds (92). In practice, a family of ablation probe tips (100) may be produced and shipped in a surgical kit. Creation of the custom surgical stent (80): The custom surgical stent (80) can be manufactured using the surgical stent design software suite that can be implemented as one or more programs, subprograms, applications, or modules. The three-dimensional digital image and at least one dental impression are imported into the surgical stent design software suite. The ablation probe tip (100) or possible ablation probe tips (100), and their corresponding specifications, are preferably known to (or provided to) the surgical stent design software suite so that the software suite can take into account the profile, dimensions, and / or capabilities (e.g., power density) of the ablation probe tip(s) (100) when designing the surgical stent (80). The surgical stent design software suite designs the surgical stent (80) with at least one surgical guide (82) and at least one mechanical stop (86) to guide and constrain the placement of the ablation probe tip (100) on the dental sketches (92).(In other words, the surgical stent design software suite calculates and provides the ideal probe positioning data, entry angle, and depth data necessary for optimal placement of the ablation probe's ablation center (124) in the target tooth outlines (92) with a total system tolerance of + / - 0.5 mm for complete control of the ablation zone positioning. This information can then be used to calculate the data required to create at least one surgical guide (82) and at least one mechanical stop (86)). The surgical stent design software suite also designs the surgical stent (80) to fit the patient's soft tissue (gums), preferably including the soft tissue covering the tooth outlines (92).The surgical stent design software suite also designs the surgical stent (80) to fit the patient's erupted teeth (e.g., the first and / or second permanent molars (95)) so that the erupted teeth act as physical supports to keep the surgical stent (80) in place. The surgical stent design software suite designs and manufactures custom surgical stents (80) according to the methods discussed in the Therapeutic Properties of Dental Sketches and known methods. Furthermore, the surgical stent design software suite preferably formats the information about the custom-designed surgical stent to be retained as at least one output file (e.g., an *.stl output file). The output files can be used to create the surgical stent (80) using, for example, 3D printing. In other cases, the output files can result in the mapping of a virtual stent (82', 86', 88j). The surgical stent design software suite can work with CBCT software or can include custom software enhancements to CBCT software that help to quickly design and manufacture custom surgical stents (80). Determining optimal settings: The surgical stent design software suite calculates and / or preferably defines the optimal settings for intraoperative ablation power and time (power dose and time). (Figure 18 shows the effects of power and time on the ablation area in an illustrative model.) Determining the ideal power and time (duration) settings for ablation takes into account factors including, but not limited to, the profile of the ablation probe systems (50) (e.g., the zone(s) (150, 160, 170) produced by the ablation probe tip(s) (100)), the dimensions of the dental outlines (calculated from the volume scan images in the surgical stent design software suite), and the patient's age (during the ages of 6 to 12 years, a patient's dental outlines will generally have a diameter in the range of 4 mm to 12 mm).The ablation dose energy and treatment times are preferably compensated incrementally for the increase in the volumes of the tooth outlines. These patient- and tooth-specific settings are stored in a database (e.g., a volume scan information technology file) for later loading into the ablation source (60) when the operator configures it or may be part of the customized surgical guidance kit (e.g., a prescription). Customized surgical equipment: The components of the customized surgical stent can be manufactured using a suite of surgical stent design software that can be implemented as one or more programs, subprograms, applications or modules to control production and / or calculate digital data (e.g., parameter settings (64) and / or treatment time settings (66)). A customized surgical kit preferably includes the components necessary for the procedure. These necessary components include, but are not limited to, at least one sterile customized surgical stent (80), at least one sterile probe tip (ablation probe tip (100)), instruction documentation (or an indication of where the instructions can be found, e.g., online), and the calculated optimum settings. ML / IZ / ZZZZ / U11» (or an indication of where the optimal settings can be found, e.g., online), and / or a patient identification key provided with the equipment. Customized surgical equipment is preferably disposable. It should be noted that some components of the customized surgical kit can be combined. For example, the instruction sheet could be a small card with a website address and the patient's identification code. The user can then enter the patient identification code into the website address to obtain the calculated optimal settings. It should be noted that “instructional documents” may be printed or accessible electronically (e.g., via a website, CD, or hard drive). The surgical kit's ablation probe tip (100) fits the patient's custom surgical stent (80). Alternatively, the surgical kit may include a family of probe tips (e.g., 2 to 10 ablation probe tips) to accommodate multiple possible depth and volume ratios of the dental outlines. The probe tip family would have probe tips with different characteristics, such as varying lengths (e.g., the distance from the mechanical tip stop (106) to the ablation center (124) and / or the distance from the mechanical tip stop (106) to the insertion end (104)), connection structure (e.g., the connection structure that couples with the handpiece (52)), and / or widths.If a family of probe tips is provided, the correct ablation probe tip (100) would be clearly indicated, or a method for determining the correct ablation probe tip (100) would be provided (e.g., color coding on the fabricated stent with a chart showing which ablation probe tip should be used for each color). Alternatively, the surgical kit may not include a probe tip but instead include a specific indication of the ablation probe tip (100) that is required (e.g., the ablation probe tip (100) that fits the patient's custom surgical stent (80)). This specific indication may include the brand, model, and size of the correct ablation probe tip (100). The ablation probe tip(s) (100) may be individually packaged (or packaged as a family), be sterile and disposable. Customized surgical kits are preferably labeled and packaged. The labeling can be customized for each package to include information such as, but not limited to, the patient's name (and / or other identifying information), part numbers, the attending physician's name (and / or other identifying information such as address), and the patient's identification code. ML / E / ZuZz / u U11» Operator use of customized surgical equipment for ablation of a dental outline (92) (without ablation of overlying gingival tissue (94)) with minimal pain and minimal potential for infection. The operator prepares the procedure by switching on the ablation generator (ablation source (60)). When the generator is switched on, the correct procedure information or the patient identification key (which can be any predetermined information or code) is preferably entered. This information then accesses a database (which can be a centrally controlled database or one of many databases) and downloads the patient's name and the pre-programmed settings for each tooth to be ablated. The system may be structured so that the pre-programmed settings cannot be modified (i.e., an operator cannot enter or adjust the power level or time settings). The handpiece (52) is preferably functionally connected to the ablation source (60). The tip of the disposable ablation probe (100) is also preferably functionally connected to the ablation handpiece (52). The handpiece (52) may have a mandrel (which may be a push-button electrical connector mandrel that provides quick and reliable setup and easy maintenance) into which the tip of the ablation probe (100) can be inserted and secured. The operator can begin the procedure by placing the surgical stent (80) on the patient's teeth before administering the local anesthetic. The local anesthetic (1 / 4 of a carpule per site) is then typically administered through the surgical guides (82) of the surgical stent (80) and directly into or around the tooth bud (92), positioning the needle tip at the predetermined location. Precise placement of the anesthetic reduces the amount required for the procedure. Once the patient is anesthetized, it is preferable to allow a waiting period to permit the anesthetic solution to dissipate physically, thus avoiding alteration of the volume of the dental prototypes. During this waiting period, the operator can functionally connect the tip of the sterile ablation probe (100) to the handpiece (52) and turn on the ablation source (60) if these steps have not already been performed. The surgical stent (80) can also be replaced at this time. When everything is ready, the operator begins to perform the ablation procedure by replacing the surgical stent (80) (if it has not already been done), grasping the handpiece (52), and introducing the tip of the self-penetrating ablation probe (100) through the surgical guide (82) to a stop to pierce and penetrate the oral mucosal tissue and reach a correct final stop position with the ablation center (124) inside the tooth outlines (92) (e.g., in the center of the tooth outlines (93)). To verify the final stop position, the ablation probe tip (100) is pressed to a final stop to secure the probe tip axis in the surgical stent (80) (and particularly in the area surrounding the surgical guide (82)) to position the ablation probe tip (100) at the predetermined angle and depth of the ablation center (124) of the probe tip in the center of the dental outlines (92). Once the ablation probe tip (100) is positioned so that the ablation center (124) is in the center of the tooth outline (92), the ablation source (60) can be activated. Activation can be performed using a direct trigger (button) or a remote trigger (e.g., a wireless foot pedal) to deliver the full energy dose according to the patient's specific time / power levels. Ablation times are determined based on system power, the predetermined volume of the tooth outline, and other parameters. The ablation device (62) will preferably monitor the progress of the procedure. The output of the ablation probe tip (100) can be monitored by the percentage of reflected energy to confirm the delivery of the appropriate ablation dose. A visual and / or audible signal can be provided to indicate successful delivery of the ablation energy when the ablation is complete. The operator then removes the ablation probe tip (100) and the surgical stent (80). No sutures are required, and there is usually very little bleeding after the procedure. The patient is free to resume normal activities immediately. Distinctions: The NEUWAVE™ microwave ablation system is described in the Background section. It is described as capable of ablating lesions with consistency and control to help protect non-target tissue. More specifically, it is described that the NEUWAVE™ system and the NEUWAVE PR probe have a burn pattern that controls the ablation distance beyond the probe tip. The NEUWAVE™ system always produces an oblong ablation zone that migrates asymmetrically upward along the probe axis. This means that the center of the ablation moves upward along the axis during the procedure, and the outer margins of the ablation zone also move upward along the axis as the ablation zone expands. The NEUWAVE system is based on coherent microwave emissions with at least a certain wavelength. Because of this, there is no physical ability to mold the ablation zone into alternative shapes using the NEUWAVE™ PR probe or the NEUWAVE system. Among the ML / E / ZuZZ / uU11y ways in which the invention described herein addresses the limitations of the PR probe is by having a stationary ablation center and eliminating the asymmetric migration of the ablation pattern upwards from the probe, while also being able to effectively shape the pattern to suit the desired ablation pattern. The Background section analyzes U.S. Patent No. 7,611,508 of Yang et al. Yang describes an antenna for microwave tumor ablation that has coaxial antenna conductors surrounded by an insulated cover of a length and size that promotes destructive interference of axial microwave energy passing in and out of the cover to limit the migration of SAR power to the skin. Yang's floating cover provides destructive cancellation or wave interference of the microwaves. By changing the position of the covers, the effective size of the heating pattern changes as a result of modifying the degree of destructive cancellation or wave interference. Yang, operating at 2.45 GHz, would have wavelengths operating at odd multiples of the wavelength, which is 1*12.2 cm (122 mm)*0.5 = 6.1 cm (61 mm) or more as higher odd multiples are used.This means that Yang operates using far-field radiation regions of the electromagnetic (EM) field surrounding the antenna where microwaves can radiate coherently. Among the ways in which the invention described herein addresses the limitations of Yang is by eliminating upward migration of the ablation pattern from the probe by having a stationary ablation center, while also being able to effectively shape the pattern to match the desired ablation pattern. Unlike the NEUWAVE PR and Yang probe designs, which are based on the far-field coherent waveform, the ablation probes described herein operate in the non-radiative near-field (near-field reactive) regions of the electromagnetic (EM) field surrounding the antenna, where microwaves radiate incoherently. Near-field reactive regions are generally considered to be wavelengths of λ / 2π ~0.159 or less. The ablation probes described herein preferably operate over a broad range of wavelengths, but for soft tissue ablation at 2.45 GHz, the near-field reactive aperture would preferably be less than 20 mm.For 12 GHz, the wavelength is shorter (e.g., 25 mm), meaning that the aperture and effective length of the probe antenna are preferably 4 mm or less to provide optimal shape and focus the targeted properties. The heat transfer layer (130) described herein is preferably able to take advantage of tissue cooling because it does not emit a coherent waveform. In sharp contrast, the antenna described in Yang's reference starts with the shortest antenna length of 22 mm from the proximal end of the ablation probe and is... ML / E / ZυZZZ / υΊ U11» lengthens in increments of h wavelength further up the ablation probe as the floating cover moves further up the axis (according to Yang's Figure 6, the distances labeled with reference numbers (62a, 62b and 62c)) making the shaping of the ablation zone in a space of less than 30 mm physically impossible. Several: It should be understood that the inventions, examples, and embodiments described herein are not limited to the materials, methods, and / or structures specifically exemplified. It should be understood that the inventions, examples, and embodiments described herein are to be considered preferred inventions, examples, and embodiments, whether or not specifically identified as such. The inventions, examples, and embodiments shown are preferred but are not intended to be limiting unless specifically claimed, in which case they may limit the scope of that particular claim. All references (including, but not limited to, publications, patents and patent applications) cited herein, whether above or below, are incorporated by reference in their entirety. The terms and expressions employed in the foregoing specification are used for descriptive purposes and not to limit the invention, and are not intended to exclude equivalents of the features shown and described. While the foregoing is a complete description of selected embodiments of the present invention, it is possible to practice the invention using various alternatives, modifications, adaptations, variations, and / or combinations and their equivalents. Those skilled in the art will appreciate that any arrangement calculated to achieve the same purpose may be substituted for the specific embodiment shown. It should also be understood that this description is intended to cover all the generic and specific features of the invention described herein and all statements regarding the scope of the invention that, in terms of language, might be said to fall within them.

Claims

1. An ablation probe tip having a shaft with an insertion end, said ablation probe tip receiving ablation means from an ablation source, said ablation probe tip for ablating the target tissue, said ablation probe tip comprising: (a) said shaft including a coaxial antenna, said coaxial antenna comprising: (i) an inner conductor; (ii) an annular dielectric insulating layer surrounding said inner conductor; and (iii) an annular outer conductor surrounding said annular dielectric insulating layer; (b) an annular opening defined in said annular outer conductor towards said insertion end; (c) an ablation center located within said inner conductor and surrounded by said annular opening;(d) an annular heat transfer layer surrounding said coaxial antenna and separated from said insertion end, such that said annular aperture is located between said annular heat transfer layer and said insertion end; (e) an annular tip cover on said insertion end, said annular tip cover surrounding and covering one end of said coaxial antenna and said annular aperture; (f) said ablation center being a focal region from which said ablation medium radiates through said annular aperture to form an ablation zone; and (g) said ablation zone having a predetermined shape selected from the group consisting of oblate, spherical, and oblong.

2. The ablation probe tip according to claim 1, said ablation zone for selective ablation of said target tissue while mitigating damage to immediately adjacent collateral tissues.

3. The tip of the ablation probe according to claim 1, wherein at least part of said target tissue is destroyed by said ablation zone.

4. The ablation probe tip according to claim 1, said predetermined shape determined by an aperture offset, said aperture offset being a distance between said ablation center and an annular edge of said annular heat transfer layer.

5. The ablation probe tip according to claim 1, said predetermined shape determined by an opening displacement, said opening displacement being a distance between said ablation center and an annular edge of said annular heat transfer layer, an oblate ablation zone having a relatively short opening displacement, an oblong ablation zone having a relatively long opening displacement, and a spherical ablation zone having an opening displacement between said opening displacements of said oblate ablation zone and said oblong ablation zone.

6. The ablation probe tip according to claim 1, said coaxial antenna further comprises an annular insulation layer surrounding said annular outer conductor, said annular heat transfer layer surrounding said annular insulation layer.

7. The ablation probe tip according to claim 1, an antenna end load positioned between said annular opening and said insertion end.

8. The ablation probe tip according to claim 1, an antenna end load positioned between said annular aperture and said insertion end, said antenna end load concentrating the energy density and increasing the power load.

9. The ablation probe tip according to claim 1, said annular heat transfer layer has high thermal conductivity and is electrically conductive.

10. The tip of the ablation probe according to claim 1, said annular opening exposes an annular ring of said annular dielectric insulating layer.

11. The ablation probe tip according to claim 1, said ablation probe tip being part of a surgical ablation kit including an ablation source, a handpiece, a stent, and a prescription.

12. The ablation probe tip according to claim 1, said ablation probe tip being part of a surgical ablation kit including an ablation source, a handpiece, a stent and a prescription, said prescription including at least one setting or parameter selected from the group consisting of: (a) ablation energy dose tolerances; (b) energy levels; and (c) energy delivery duration.

13. The ablation probe tip according to claim 1, said ablation probe tip for working in conjunction with a stent, said stent having a surgical guide, said surgical guide guides said ablation probe tip so that said MLE / E / ZuZZ / u / U11y ablation center is within the tissue.

14. The ablation probe tip according to claim 1, said ablation center being a stationary ablation center in the sense that it does not migrate in relation to said axis.

15. The tip of the ablation probe according to claim 1, said coaxial antenna being a near-field antenna that prevents said ablation center from migrating upwards from said axis away from said insertion end.

16. The tip of the ablation probe according to claim 1, said coaxial antenna being a near-field reactive antenna that prevents said ablation center from migrating upwards from said axis away from said insertion end.

17. The ablation probe tip according to claim 1, wherein said annular heat transfer layer blocks said ablation means from migrating upwards along said axis away from said insertion end, and said annular heat transfer layer allows thermal energy from said ablation zone to be conducted upwards along said axis away from said insertion end.

18. The ablation probe tip according to claim 1, said ablation probe tip being part of an ablation probe system having intraoperative maximum temperature control selected from the group consisting of: (a) passive cooling; (b) active cooling; and (c) a combination of passive and active cooling.

19. The ablation probe tip according to claim 1, said annular heat transfer layer being turned off by the transfer of thermal energy from said annular heat transfer layer into the soft tissue surrounding said annular heat transfer layer.

20. The ablation probe tip according to claim 1, said ablation probe tip being part of an ablation probe system having intraoperative control of a volume of said ablation zone.

21. The ablation probe tip according to claim 1, said ablation probe tip being part of an ablation probe system having intraoperative control of a diameter of said ablation zone.

22. The ablation probe tip according to claim 1, said ablation probe tip and said ablation means together enable at least one intraoperative control selected from the group consisting of: (a) position of said ablation zone; (b) centering of said ablation zone; (c) maximum temperature of said ablation zone; (d) volume of said ablation zone; and (e) diameter of said ablation zone.

23. The ablation probe tip according to claim 1, said ablation probe tip being a microablation probe tip.

24. The ablation probe tip according to claim 1, said ablation probe tip being a microwave ablation probe tip.

25. The ablation probe tip according to claim 1, said ablation probe tip being a microwave ablation probe tip for receiving microwave energy from said ablation source as said ablation means, said microwave energy being delivered to said target tissue through said ablation probe tip.

26. The ablation probe tip according to claim 1, said ablation probe tip is a microwave ablation probe tip for receiving microwave energy from said ablation source as said ablation medium, said ablation source providing microwave energy at frequencies ranging from 500 MHz to 20 GHz, said microwave energy delivered to said target tissue through said ablation probe tip.

27. The ablation probe tip according to claim 1, said ablation probe tip being a radiofrequency ablation probe tip.

28. An ablation probe tip having a shaft with an insertion end, said ablation probe tip receiving ablation means from an ablation source, said ablation probe tip for ablating the target tissue, said ablation probe tip comprising: (a) said shaft including a coaxial antenna; (b) an annular aperture defined in at least one outer layer of said coaxial antenna towards said insertion end; (c) an ablation center located within said coaxial antenna and surrounded by said annular aperture; (d) an annular heat transfer layer surrounding said coaxial antenna and separated from said insertion end, such that said annular aperture is located between said annular heat transfer layer and said insertion end; (e) said ablation center being a focal region from which said ablation means radiates through said annular aperture to form an ablation zone;and ivia / t / zuzz / uiu 11 and (f) said ablation zone has a predetermined shape selected from the group consisting of oblate, spherical and oblong.; 29. The ablation probe tip according to claim 28, said ablation zone for selective ablation of said target tissue while mitigating damage to immediately adjacent collateral tissues.

30. The tip of the ablation probe according to claim 28, wherein at least part of said target tissue is destroyed by said ablation zone.

31. The ablation probe tip according to claim 28, said coaxial antenna comprises: (a) an inner conductor; (b) an annular dielectric insulating layer surrounding said inner conductor; and (c) an annular outer conductor surrounding said annular dielectric insulating layer.

32. The ablation probe tip according to claim 28 further comprises an annular tip cover at said insertion end, said annular tip cover surrounding and covering one end of said coaxial antenna and said annular opening.

33. The ablation probe tip according to claim 28, said predetermined shape determined by an opening offset, said opening offset being a distance between said ablation center and an annular edge of said annular heat transfer layer.

34. The ablation probe tip according to claim 28, said predetermined shape determined by an opening offset, said opening offset being a distance between said ablation center and an annular edge of said annular heat transfer layer, an oblate ablation zone having a relatively short opening offset, an oblong ablation zone having a relatively long opening offset, and a spherical ablation zone having an opening offset between said opening offsets of said oblate ablation zone and said oblong ablation zone.

35. The tip of the ablation probe according to claim 28, said coaxial antenna further comprises an annular insulation layer surrounding said coaxial antenna, said annular heat transfer layer surrounding said annular insulation layer.

36. The ablation probe tip according to claim 28, an antenna end load positioned between said annular aperture and said insertion end. ML / E / ZuZZ / u U11» 37. The ablation probe tip according to claim 28, an antenna end load positioned between said annular opening and said insertion end, said antenna end load concentrating the energy density and increasing the power load.

38. The ablation probe tip according to claim 28, said annular heat transfer layer has high thermal conductivity and is electrically conductive.

39. The ablation probe tip according to claim 28, said coaxial antenna includes an inner conductor, an annular dielectric insulating layer surrounding said inner conductor, and an annular outer conductor surrounding said annular dielectric insulating layer, said annular opening exposing an annular ring of said annular dielectric insulating layer.

40. The ablation probe tip according to claim 28, said ablation probe tip being part of a surgical ablation kit including an ablation source, a handpiece, a stent, and a prescription.

41. The ablation probe tip according to claim 28, said ablation probe tip being part of a surgical ablation kit including an ablation source, a handpiece, a stent and a prescription, said prescription including at least one setting or parameter selected from the group consisting of: (a) ablation energy dose tolerances; (b) energy levels; and (c) the duration of energy delivery.

42. The ablation probe tip according to claim 28, said ablation probe tip for working in conjunction with a stent, said stent having a surgical guide, said surgical guide guides said ablation probe tip so that said ablation center is within the tissue.

43. The ablation probe tip according to claim 28, said ablation center being a stationary ablation center in the sense that it does not migrate in relation to said axis.

44. The tip of the ablation probe according to claim 28, said coaxial antenna being a near-field antenna that prevents said ablation center from migrating upwards from said axis away from said insertion end.

45. The tip of the ablation probe according to claim 28, said coaxial antenna being a near-field reactive antenna that prevents said ablation center from migrating upwards from said axis away from said insertion end.

46. ​​The ablation probe tip according to claim 28, ML / IZ / ZZZZ / UII and wherein said annular heat transfer layer blocks said ablation means from migrating upwards along said axis away from said insertion end, and said annular heat transfer layer allows thermal energy from said ablation zone to be conducted upwards along said axis away from said insertion end.

47. The ablation probe tip according to claim 28, said ablation probe tip being part of an ablation probe system having intraoperative maximum temperature control selected from the group consisting of: (a) Passive cooling; (b) active cooling; and (c) a combination of passive and active cooling.

48. The ablation probe tip according to claim 28, said annular heat transfer layer being turned off by the transfer of thermal energy from said annular heat transfer layer into the soft tissue surrounding said annular heat transfer layer.

49. The ablation probe tip according to claim 28, said ablation probe tip being part of an ablation probe system having intraoperative control of a volume of said ablation zone.

50. The ablation probe tip according to claim 28, said ablation probe tip being part of an ablation probe system having intraoperative control of a diameter of said ablation zone.

51. The ablation probe tip according to claim 28, said ablation probe tip and said ablation means together enable at least one intraoperative control selected from the group consisting of: (a) position of said ablation zone; (b) centering of said ablation zone; (c) maximum temperature of said ablation zone; (d) volume of said ablation zone; and (e) diameter of said ablation zone.

52. The ablation probe tip according to claim 28, said ablation probe tip being a microablation probe tip.

53. The ablation probe tip according to claim 28, said ablation probe tip being a microwave ablation probe tip.

54. The ablation probe tip according to claim 28, said ablation probe tip being a microwave ablation probe tip for receiving microwave energy from said ablation source as said ablation means, MLE / E / ZUZZ / Ul Ul 1 and said microwave energy being delivered to said target tissue through said ablation probe tip.

55. The ablation probe tip according to claim 28, said ablation probe tip is a microwave ablation probe tip for receiving microwave energy from said ablation source as said ablation means, said ablation source providing microwave energy at frequencies ranging from 500 MHz to 20 GHz, said microwave energy delivered to said target tissue through said ablation probe tip.

56. The ablation probe tip according to claim 28, said ablation probe tip being a radiofrequency ablation probe tip.

57. An ablation probe tip having a shaft with an insertion end, said ablation probe tip receiving ablation means from an ablation source, said ablation probe tip for ablating the target tissue, said ablation probe tip comprising: (a) said shaft including a coaxial antenna; (b) an annular aperture defined in at least one outer layer of said coaxial antenna towards said insertion end; (c) an ablation center located within said coaxial antenna and surrounded by said annular aperture, said ablation center being a focal region from which said ablation means radiate through said annular aperture to form an ablation zone;(d) an annular heat transfer layer surrounding said coaxial antenna, said annular heat transfer layer having an annular edge that is the portion of said annular heat transfer layer closest to said annular opening, said annular edge being spaced from said insertion end such that said annular opening is between said annular heat transfer layer and said insertion end; (e) an aperture offset, said aperture offset being a distance between said ablation center and said annular edge of said annular heat transfer layer;and (f) said ablation zone has a predetermined shape determined by the displacement of the aperture, such that a displacement of the aperture of relatively short length makes said ablation zone oblate, a displacement of the aperture of relatively long length makes said ablation zone oblong, and a displacement of the aperture of medium length makes said ablation zone spherical.; 58. The ablation probe tip according to claim 57, said ablation zone for selective ablation of said target tissue while mitigating damage to ML / t / ZUZZ / UI Ul iy the immediately adjacent collateral tissues.

59. The tip of the ablation probe according to claim 57, wherein at least part of said target tissue is destroyed by said ablation zone.

60. The tip of the ablation probe according to claim 57, said coaxial antenna further comprises an annular insulation layer surrounding said coaxial antenna, said annular heat transfer layer surrounding said annular insulation layer.

61. The ablation probe tip according to claim 57, an antenna end load positioned between said annular opening and said insertion end.

62. The ablation probe tip according to claim 57, an antenna end load positioned between said annular aperture and said insertion end, said antenna end load concentrating the energy density and increasing the power load.

63. The ablation probe tip according to claim 57, said annular heat transfer layer has high thermal conductivity and is electrically conductive.

64. The ablation probe tip according to claim 57, said coaxial antenna includes an inner conductor, an annular dielectric insulating layer surrounding said inner conductor, and an annular outer conductor surrounding said annular dielectric insulating layer, said annular opening exposing an annular ring of said annular dielectric insulating layer.

65. The ablation probe tip according to claim 57, said ablation probe tip being part of a surgical ablation kit including an ablation source, a handpiece, a stent, and a prescription.

66. The ablation probe tip according to claim 57, said ablation probe tip being part of a surgical ablation kit including an ablation source, a handpiece, a stent and a prescription, said prescription including at least one setting or parameter selected from the group consisting of: (a) ablation energy dose tolerances; (b) energy levels; and (c) the duration of energy delivery.

67. The ablation probe tip according to claim 57, said ablation probe tip for working in conjunction with a stent, said stent having a surgical guide, said surgical guide guiding said ablation probe tip so that said ablation center is within the tissue. ML / E / ZuZZ / u U11 9 68. The ablation probe tip according to claim 57, said ablation center being a stationary ablation center in the sense that it does not migrate in relation to said axis.

69. The tip of the ablation probe according to claim 57, said coaxial antenna being a near-field antenna that prevents said ablation center from migrating upwards from said axis away from said insertion end.

70. The tip of the ablation probe according to claim 57, said coaxial antenna being a near-field reactive antenna that prevents said ablation center from migrating upwards from said axis away from said insertion end.

71. The ablation probe tip according to claim 57, wherein said annular heat transfer layer blocks said ablation means from migrating upwards along said axis away from said insertion end, and said annular heat transfer layer allows thermal energy from said ablation zone to be conducted upwards along said axis away from said insertion end.

72. The ablation probe tip according to claim 57, said ablation probe tip being part of an ablation probe system having intraoperative maximum temperature control selected from the group consisting of: (a) passive cooling; (b) active cooling; and (c) a combination of passive and active cooling.

73. The ablation probe tip according to claim 57, said annular heat transfer layer being turned off by the transfer of thermal energy from said annular heat transfer layer into the soft tissue surrounding said annular heat transfer layer.

74. The ablation probe tip according to claim 57, said ablation probe tip being part of an ablation probe system having intraoperative control of a volume of said ablation zone.

75. The ablation probe tip according to claim 57, said ablation probe tip being part of an ablation probe system having intraoperative control of a diameter of said ablation zone.

76. The ablation probe tip according to claim 57, said ablation probe tip and said ablation means together enable at least one selected intraoperative control group consisting of: (a) position of said ablation zone; (b) shape of said ablation zone; (c) centering of said ablation zone; (d) maximum temperature of said ablation zone; (e) volume of said ablation zone; and (f) diameter of said ablation zone.

77. The ablation probe tip according to claim 57, said ablation probe tip being a microablation probe tip.

78. The ablation probe tip according to claim 57, said ablation probe tip being a microwave ablation probe tip.

79. The ablation probe tip according to claim 57, said ablation probe tip being a microwave ablation probe tip for receiving microwave energy from said ablation source as said ablation means, said microwave energy being delivered to said target tissue through said ablation probe tip.

80. The ablation probe tip according to claim 57, said ablation probe tip is a microwave ablation probe tip for receiving microwave energy from said ablation source as said ablation means, said ablation source providing microwave energy at frequencies ranging from 500 MHz to 20 GHz, said microwave energy delivered to said target tissue through said ablation probe tip.

81. The ablation probe tip according to claim 57, said ablation probe tip being a radiofrequency ablation probe tip.

82. An ablation probe tip having a shaft with an insertion end, said ablation probe tip receiving ablation means from an ablation source, said ablation probe tip for ablating the target tissue, said ablation probe tip comprising: (a) said shaft including a coaxial antenna, said coaxial antenna being a near-field antenna; (b) an annular aperture defined in at least one outer layer of said coaxial antenna towards said insertion end; (c) an ablation center located within said coaxial antenna and surrounded by said annular aperture, said ablation center being a focal region from which said ablation means radiate through said annular aperture to form an ablation zone; and (d) said near-field antenna preventing said ablation center from migrating upwards along said shaft away from said insertion end.

83. The ablation probe tip according to claim 82, said ablation zone for selective ablation of said target tissue while mitigating damage to immediately adjacent collateral tissues.

84. The tip of the ablation probe according to claim 82, wherein at least part of said target tissue is destroyed by said ablation zone.

85. The ablation probe tip according to claim 82 further comprises an annular heat transfer layer surrounding said coaxial antenna.

86. The ablation probe tip according to claim 82 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is between said annular heat transfer layer and said insertion end.

87. The ablation probe tip according to claim 82, said ablation zone having a predetermined shape selected from the group consisting of oblate, spherical and oblong.

88. The ablation probe tip according to claim 82 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is located between said annular heat transfer layer and said insertion end, said ablation zone having a predetermined shape, said predetermined shape being determined by an opening offset, said opening offset being a distance between said ablation center and an annular edge of said annular heat transfer layer.

89. The ablation probe tip according to claim 82 further comprises an annular heat transfer layer surrounding the coaxial antenna and spaced from the insertion end such that the annular opening is between the annular heat transfer layer and the insertion end, the ablation zone having a predetermined shape, the predetermined shape being determined by an opening offset, the opening offset being a distance between the ablation center and an annular edge of the annular heat transfer layer, an oblate ablation zone having a relatively short opening offset, an oblong ablation zone having a relatively long opening offset, and a spherical ablation zone having an opening offset between the opening offsets of the oblate ablation zone and the oblong ablation zone.

90. The ablation probe tip according to claim 82 further comprises an annular heat transfer layer surrounding said coaxial antenna, said coaxial antenna further comprises an annular insulation layer surrounding said coaxial antenna in an annular manner, said annular heat transfer layer surrounding said annular insulation layer.

91. The ablation probe tip according to claim 82, an antenna end load positioned between said annular opening and said insertion end.

92. The ablation probe tip according to claim 82, an antenna end load positioned between said annular aperture and said insertion end, said antenna end load concentrating the energy density and increasing the power load.

93. The ablation probe tip according to claim 82 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is between said annular heat transfer layer and said insertion end, said annular heat transfer layer having high thermal conductivity and being electrically conductive.

94. The ablation probe tip according to claim 82, said coaxial antenna includes an inner conductor, an annular dielectric insulating layer surrounding said inner conductor, and an annular outer conductor surrounding said annular dielectric insulating layer, said annular opening exposing an annular ring of said annular dielectric insulating layer.

95. The ablation probe tip according to claim 82, said ablation probe tip being part of a surgical ablation kit including an ablation source, a handpiece, a stent, and a prescription.

96. The ablation probe tip according to claim 82, said ablation probe tip being part of a surgical ablation kit including an ablation source, a handpiece, a stent and a prescription, said prescription including at least one setting or parameter selected from the group consisting of: (a) ablation energy dose tolerances; (b) energy levels; and (c) the duration of energy delivery.

97. The ablation probe tip according to claim 82, said ablation probe tip for working in conjunction with a stent, said stent having a surgical guide, said surgical guide guides said ablation probe tip so that said ablation center is within the tissue.

98. The ablation probe tip according to claim 82, said ablation center being a stationary ablation center in the sense that it does not migrate in relation to said axis.

99. The ablation probe tip according to claim 82, MLE / E / ZUZZ / Ul Ul 1U, said coaxial antenna being a near-field reactive antenna.

100. The ablation probe tip according to claim 82 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is located between said annular heat transfer layer and said insertion end, wherein said annular heat transfer layer blocks said ablation means from migrating upwards along said axis away from said insertion end, and said annular heat transfer layer permits thermal energy from said ablation zone to be conducted upwards along said axis away from said insertion end.

101. The ablation probe tip according to claim 82, said ablation probe tip being part of an ablation probe system having intra-operational maximum temperature control selected from the group consisting of: (a) Passive cooling; (b) active cooling; and (c) a combination of passive and active cooling.

102. The ablation probe tip according to claim 82 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is located between said annular heat transfer layer and said insertion end, said annular heat transfer layer being turned off by the transfer of thermal energy from said annular heat transfer layer to the soft tissue surrounding said annular heat transfer layer.

103. The ablation probe tip according to claim 82, said ablation probe tip being part of an ablation probe system having intraoperative control of a volume of said ablation zone.

104. The ablation probe tip according to claim 82, said ablation probe tip being part of an ablation probe system having intraoperative control of a diameter of said ablation zone.

105. The ablation probe tip according to claim 82, said ablation probe tip and said ablation means together enable at least one selected intraoperative control of the group consisting of: (a) position of said ablation zone; (b) shape of said ablation zone; (c) centering of said ablation zone; (d) maximum temperature of said ablation zone; (e) volume of said ablation zone; and (f) diameter of said ablation zone.

106. The ablation probe tip according to claim 82, said ablation probe tip being a microablation probe tip.

107. The ablation probe tip according to claim 82, said ablation probe tip being a microwave ablation probe tip.

108. The ablation probe tip according to claim 82, said ablation probe tip being a microwave ablation probe tip for receiving microwave energy from said ablation source as said ablation means, said microwave energy being delivered to said target tissue through said ablation probe tip.

109. The ablation probe tip according to claim 82, said ablation probe tip being a microwave ablation probe tip for receiving microwave energy from said ablation source as said ablation means, said ablation source providing microwave energy at frequencies ranging from 500 MHz to 20 GHz, said microwave energy delivered to said target tissue through said ablation probe tip.

110. The ablation probe tip according to claim 82, said ablation probe tip being a radiofrequency ablation probe tip.

111. An ablation probe tip having a shaft with an insertion end, said ablation probe tip receiving ablation means from an ablation source, said ablation probe tip for ablating the target tissue, said ablation probe tip comprising: (a) said shaft including a coaxial antenna, said coaxial antenna being a near-field antenna; (b) an annular aperture defined in at least one outer layer of said coaxial antenna towards said insertion end; (c) an ablation center located within said coaxial antenna and surrounded by said annular aperture, said ablation center being a focal region from which said ablation means radiate through said annular aperture to form an ablation zone; and (d) said near-field antenna having a predetermined shape selected from the group consisting of oblate, spherical, and oblong.

112. The ablation probe tip according to claim 111, said ablation zone for selectively ablating said target tissue while mitigating damage to immediately adjacent collateral tissues.

113. The tip of the ablation probe according to claim 111, wherein at least part of said target tissue is destroyed by said ablation zone.

114. The tip of the ablation probe according to claim 111, said near-field antenna prevents said ablation center from migrating upwards from said axis away from said insertion end.

115. The ablation probe tip according to claim 111 further comprises an annular heat transfer layer surrounding said coaxial antenna.

116. The ablation probe tip according to claim 111 further comprises an annular heat transfer layer surrounding said coaxial antenna and separated from said insertion end, such that said annular opening is between said annular heat transfer layer and said insertion end.

117. The ablation probe tip according to claim 111, said ablation zone having a predetermined shape selected from the group consisting of oblate, spherical and oblong.

118. The ablation probe tip according to claim 111 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is located between said annular heat transfer layer and said insertion end, said ablation zone having a predetermined shape, said predetermined shape being determined by an opening offset, said opening offset being a distance between said ablation center and an annular edge of said annular heat transfer layer.

119. The ablation probe tip according to claim 111 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end such that said annular opening is between said annular heat transfer layer and said insertion end, said ablation zone having a predetermined shape, said predetermined shape determined by an opening offset, said opening offset being a distance between said ablation center and an annular edge of said annular heat transfer layer, an oblate ablation zone having a relatively short opening offset, an oblong ablation zone having a relatively long opening offset, and a spherical ablation zone having an opening offset between said opening offsets of said oblate ablation zone and said oblong ablation zone.

120. The ablation probe tip according to claim 111 further comprises an annular heat transfer layer surrounding said coaxial antenna, said coaxial antenna further comprises an annular insulation layer surrounding said coaxial antenna in an annular manner, said annular heat transfer layer surrounding said annular insulation layer.

121. The ablation probe tip according to claim 111, an antenna end load positioned between said annular opening and said insertion end.

122. The ablation probe tip according to claim 111, an antenna end load positioned between said annular aperture and said insertion end, said antenna end load concentrating the energy density and increasing the power load.

123. The ablation probe tip according to claim 111 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is between said annular heat transfer layer and said insertion end, said annular heat transfer layer having high thermal conductivity and being electrically conductive.

124. The ablation probe tip according to claim 111, said coaxial antenna includes an inner conductor, an annular dielectric insulating layer surrounding said inner conductor, and an annular outer conductor surrounding said annular dielectric insulating layer, said annular opening exposing an annular ring of said annular dielectric insulating layer.

125. The ablation probe tip according to claim 111, said ablation probe tip being part of a surgical ablation kit including an ablation source, a handpiece, a stent, and a prescription.

126. The ablation probe tip according to claim 111, said ablation probe tip being part of a surgical ablation kit including an ablation source, a handpiece, a stent and a prescription, said prescription including at least one setting or parameter selected from the group consisting of: (a) ablation energy dose tolerances; (b) energy levels; and (c) the duration of energy delivery.

127. The ablation probe tip according to claim 111, said ablation probe tip for working in conjunction with a stent, said stent having a surgical guide, said surgical guide guides said ablation probe tip so that said ablation center is within the tissue.

128. The ablation probe tip according to claim 111, said ablation center being a stationary ablation center in the sense that it does not migrate relative to said axis.

129. The tip of the ablation probe according to claim 111, said coaxial antenna being a near-field reactive antenna.

130. The ablation probe tip according to claim 111 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is located between said annular heat transfer layer and said insertion end, wherein said annular heat transfer layer blocks said ablation means from migrating upwards along said axis away from said insertion end, and said annular heat transfer layer permits thermal energy from said ablation zone to be conducted upwards along said axis away from said insertion end.

131. The ablation probe tip according to claim 111, said ablation probe tip being part of an ablation probe system having intra-operational maximum temperature control selected from the group consisting of: (a) passive cooling; (b) active cooling; and (c) a combination of passive and active cooling.

132. The ablation probe tip according to claim 111 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is located between said annular heat transfer layer and said insertion end, said annular heat transfer layer being turned off by the transfer of thermal energy from said annular heat transfer layer to the soft tissue surrounding said annular heat transfer layer.

133. The ablation probe tip according to claim 111, said ablation probe tip is part of an ablation probe system having intraoperative control of a volume of said ablation zone.

134. The ablation probe tip according to claim 111, said ablation probe tip being part of an ablation probe system having intraoperative control of a diameter of said ablation zone.

135. The ablation probe tip according to claim 111, said ablation probe tip and said ablation means together enable at least one intraoperative control selected from the group consisting of: (a) position of said ablation zone; (b) shape of said ablation zone; (c) centering of said ablation zone; (d) maximum temperature of said ablation zone; (e) volume of said ablation zone; and (f) diameter of said ablation zone.

136. The ablation probe tip according to claim 111, said ablation probe tip being a microablation probe tip.

137. The ablation probe tip according to claim 111, said ablation probe tip being a microwave ablation probe tip.

138. The ablation probe tip according to claim 111, said ablation probe tip being a microwave ablation probe tip for receiving microwave energy from said ablation source as said ablation means, said microwave energy being delivered to said target tissue through said ablation probe tip.

139. The ablation probe tip according to claim 111, said ablation probe tip being a microwave ablation probe tip for receiving microwave energy from said ablation source as said ablation means, said ablation source providing microwave energy at frequencies ranging from 500 MHz to 20 GHz, said microwave energy delivered to said target tissue through said ablation probe tip.

140. The ablation probe tip according to claim 111, said ablation probe tip being a radiofrequency ablation probe tip.

141. An ablation probe tip having a shaft with an insertion end, said ablation probe tip receiving ablation means from an ablation source, said ablation probe tip for ablating the target tissue, said ablation probe tip comprising: (a) said shaft including a coaxial antenna, said coaxial antenna being a near-field antenna; (b) an annular aperture defined in at least one outer layer of said coaxial antenna towards said insertion end; (c) an ablation center located within said coaxial antenna and surrounded by said annular aperture, said ablation center being a focal region from which said ablation means radiate through said annular aperture to form an ablation zone; and (d) said ablation center being a stationary ablation center.

142. The ablation probe tip according to claim 141, said ablation zone for selectively ablating said target tissue while mitigating damage to immediately adjacent collateral tissues.

143. The tip of the ablation probe according to claim 141, wherein at least part of said target tissue is destroyed by said ablation zone.

144. The tip of the ablation probe according to claim 141, said near-field antenna prevents said ablation center from migrating upwards from said axis away from said insertion end.

145. The ablation probe tip according to claim 141 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is located between said annular heat transfer layer and said insertion end, wherein said annular heat transfer layer prevents said ablation center from migrating upwards along said axis away from said insertion end.

146. The ablation probe tip according to claim 141 further comprises an annular heat transfer layer surrounding said coaxial antenna.

147. The ablation probe tip according to claim 141 further comprises an annular heat transfer layer surrounding said coaxial antenna and separated from said insertion end, such that said annular opening is between said annular heat transfer layer and said insertion end.

148. The ablation probe tip according to claim 141, said ablation zone having a predetermined shape selected from the group consisting of oblate, spherical and oblong.

149. The ablation probe tip according to claim 141 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is located between said annular heat transfer layer and said insertion end, said ablation zone having a predetermined shape, said predetermined shape being determined by an opening offset, said opening offset being a distance between said ablation center and an annular edge of said annular heat transfer layer.

150. The ablation probe tip according to claim 141 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is between said annular heat transfer layer and said insertion end, said ablation zone having a predetermined shape, said predetermined shape being determined by an aperture offset, said aperture offset being a distance between said ablation center and an annular edge of said annular heat transfer layer, an oblate ablation zone having a relatively short aperture offset, an oblong ablation zone having a relatively long aperture offset, and a spherical ablation zone having an aperture offset between said aperture offsets of said oblate ablation zone and said oblong ablation zone.

151. The ablation probe tip according to claim 141 further comprises an annular heat transfer layer surrounding said coaxial antenna, said coaxial antenna further comprises an annular insulation layer surrounding said coaxial antenna, said annular heat transfer layer surrounding said annular insulation layer.

152. The ablation probe tip according to claim 141, an antenna end load positioned between said annular opening and said insertion end.

153. The ablation probe tip according to claim 141, an antenna end load positioned between said annular aperture and said insertion end, said antenna end load concentrating the energy density and increasing the power load.

154. The ablation probe tip according to claim 141 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is between said annular heat transfer layer and said insertion end, said annular heat transfer layer having high thermal conductivity and being electrically conductive.

155. The ablation probe tip according to claim 141, said coaxial antenna includes an inner conductor, an annular dielectric insulating layer surrounding said inner conductor, and an annular outer conductor surrounding said annular dielectric insulating layer, said annular opening exposing an annular ring of said annular dielectric insulating layer.

156. The ablation probe tip according to claim 141, said ablation probe tip being part of a surgical ablation kit including an ablation source, a handpiece, a stent, and a prescription.

157. The ablation probe tip according to claim 141, said ablation probe tip being part of a surgical ablation kit including an ablation source, a handpiece, a stent and a prescription, said prescription including at least one setting or parameter selected from the group consisting of: (a) ablation energy dose tolerances; (b) energy levels; and (c) the duration of energy delivery.

158. The ablation probe tip according to claim 141, said ablation probe tip for working in conjunction with a stent, said stent having a surgical guide, said surgical guide guides said ablation probe tip so that said ablation center is within the tissue.

159. The tip of the ablation probe according to claim 141, said coaxial antenna being a near-field reactive antenna.

160. The ablation probe tip according to claim 141 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is located between said annular heat transfer layer and said insertion end, wherein said annular heat transfer layer blocks said ablation means from migrating upwards along said axis away from said insertion end, and said annular heat transfer layer permits thermal energy from said ablation zone to be conducted upwards along said axis away from said insertion end.

161. The ablation probe tip according to claim 141, said ablation probe tip being part of an ablation probe system having intra-operational maximum temperature control selected from the group consisting of: (a) Passive cooling; (b) active cooling; and (c) a combination of passive and active cooling.

162. The ablation probe tip according to claim 141 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is located between said annular heat transfer layer and said insertion end, said annular heat transfer layer being turned off by the transfer of thermal energy from said annular heat transfer layer to the soft tissue surrounding said annular heat transfer layer.

163. The ablation probe tip according to claim 141, said ablation probe tip being part of an ablation probe system having intraoperative control of a volume of said ablation zone.

164. The ablation probe tip according to claim 141, said ablation probe tip being part of an ablation probe system having intraoperative control of a diameter of said ablation zone.

165. The ablation probe tip according to claim ML / E / ZuZZ / uU11» 141, said ablation probe tip and said ablation means together enable at least one intraoperative control selected from the group consisting of: (a) position of said ablation zone; (b) shape of said ablation zone; (c) centering of said ablation zone; (d) maximum temperature of said ablation zone; (e) volume of said ablation zone; and (f) diameter of said ablation zone.

166. The ablation probe tip according to claim 141, said ablation probe tip being a microablation probe tip.

167. The ablation probe tip according to claim 141, said ablation probe tip being a microwave ablation probe tip.

168. The ablation probe tip according to claim 141, said ablation probe tip being a microwave ablation probe tip for receiving microwave energy from said ablation source as said ablation means, said microwave energy being delivered to said target tissue through said ablation probe tip.

169. The ablation probe tip according to claim 141, said ablation probe tip being a microwave ablation probe tip for receiving microwave energy from said ablation source as said ablation means, said ablation source providing microwave energy at frequencies ranging from 500 MHz to 20 GHz, said microwave energy delivered to said target tissue through said ablation probe tip.

170. The ablation probe tip according to claim 141, said ablation probe tip being a radiofrequency ablation probe tip.

171. An ablation probe tip having a shaft with an insertion end, said ablation probe tip receiving ablation means from an ablation source, said ablation probe tip for ablating the target tissue from within, said ablation probe tip comprising: (a) said shaft including a coaxial antenna, said coaxial antenna comprising: (i) an inner conductor; (ii) an annular dielectric insulating layer surrounding said inner conductor; and (iii) an annular outer conductor surrounding said annular dielectric insulating layer; (b) an annular opening defined in said annular outer conductor toward said insertion end; (c) an ablation center located within said inner conductor and surrounded by said annular opening;(d) an annular heat transfer layer surrounding said coaxial antenna and separated from said insertion end, such that said annular aperture is located between said annular heat transfer layer and said insertion end; (e) an annular tip cover on said insertion end, said annular tip cover surrounding and covering one end of said coaxial antenna and said annular aperture; (f) said ablation center being a focal region from which said ablation medium radiates through said annular aperture to form an ablation zone; and (g) said ablation zone having a predetermined shape selected from the group consisting of oblate, spherical, and oblong.

172. The ablation probe tip according to claim 171, wherein said insertion end is a self-inserting insertion end.

173. The ablation probe tip according to claim 171 or according to claim 172, said predetermined shape determined by an opening offset, said opening offset being a distance between said ablation center and an annular edge of said annular heat transfer layer.

174. The ablation probe tip according to claim 172, wherein an oblate ablation zone having a relatively short opening displacement, an oblong ablation zone having a relatively long opening displacement, and a spherical ablation zone having an opening displacement between said opening displacements of said oblate ablation zone and said oblong ablation zone.

175. The ablation probe tip according to claim 173 or according to claim 174, wherein: the ablation zone is an oblate-shaped ablation zone and the aperture displacement is less than 1 mm; the ablation zone is a spherical-shaped ablation zone and the aperture displacement is in the range of 1 mm to 4 mm; or the ablation zone is an oblong-shaped ablation zone and the aperture displacement is greater than 4 mm.

176. The tip of the ablation probe according to any of the preceding claims, said coaxial antenna further comprises an annular insulation layer surrounding said outer annular conductor, said annular heat transfer layer surrounding said annular insulation layer. ML / E / ZuZZ / uII and 177. The ablation probe tip according to any of the preceding claims, wherein the annular heat transfer layer is an outer layer.

178. The ablation probe tip according to any of the preceding claims, further comprising an antenna end load positioned between said annular opening and said insertion end.

179. The tip of the ablation probe according to one of the preceding claims 178, said final antenna load concentrates the energy density and increases the power load.

180. The tip of the ablation probe according to one of the preceding claims, said annular heat transfer layer has high thermal conductivity and is electrically conductive.

181. The tip of the ablation probe according to one of the preceding claims, said annular opening exposes an annular ring of said annular dielectric insulating layer.

182. The ablation probe tip according to any preceding claim, wherein the tip cover is made of a material having the following properties: high radiotransparency; low thermal conductivity; and electrically non-conductive.

183. The ablation probe tip according to any preceding claim, wherein the annular heat transfer layer is configured to, in use, be switched off by the transfer of thermal energy from said annular heat transfer layer to the soft tissue surrounding said annular heat transfer layer.

184. The ablation probe tip according to any of claims 182 to 183, wherein, during use, the ablation center remains substantially stationary.

185. The ablation probe tip according to any of the preceding claims, wherein said coaxial antenna is a near-field antenna wherein, in use, the output of the ablation means carries energy acting on the near-field reactive region of the antenna.

186. The ablation probe tip according to claim 185, wherein the coaxial antenna has an effective antenna length of λ / 2π or less.

187. A surgical ablation kit comprising an MA / 1 Ul ablation probe tip according to one of the preceding claims, an ablation source, a handpiece, a stent, and a prescription.

188. The surgical ablation equipment according to claim 171, said prescription includes at least one setting or parameter selected from the group consisting of: (a) ablation energy dose tolerances; (b) energy levels; and (c) the duration of energy delivery.

189. The ablation surgical equipment according to claim 188, said surgical equipment, in use, has intraoperative maximum temperature control selected from the group consisting of: (a) Passive cooling; (b) active cooling; and (c) a combination of passive and active cooling.

190. The ablation surgical equipment according to claim 189, said surgical equipment, in use, permits at least one selected intraoperative control of the group consisting of: (a) volume of said ablation zone; and (b) the diameter of said ablation zone.

191. An ablation probe tip having a shaft with an insertion end, said ablation probe tip receiving ablation means from an ablation source, said ablation probe tip for ablating the target tissue, said ablation probe tip comprising: (a) said shaft including a coaxial antenna; (b) an annular aperture defined in at least one outer layer of said coaxial antenna towards said insertion end; (c) an ablation center located within said coaxial antenna and surrounded by said annular aperture, said ablation center being a focal region from which said ablation means radiate through said annular aperture to form an ablation zone; and (d) said ablation zone having a predetermined power charge density in said ablation zone.

192. The ablation probe tip according to claim 191, said ablation zone for selectively ablating said target tissue while mitigating damage to immediately adjacent collateral tissues.

193. The tip of the ablation probe according to claim 191, wherein at least part of said target tissue is destroyed by said ablation zone. MLE / E / ZUZZ / Ul Ul 1y 194. The ablation probe tip according to claim 191, said annular opening being a short annular opening to create a short active heating zone surrounding said annular opening, said short active heating zone to create a high power load in said ablation zone.

195. The ablation probe tip according to claim 191, said annular opening being a short annular opening to create a short active heating zone surrounding said annular opening, said short active heating zone to create high peak temperatures in said ablation zone.

196. The ablation probe tip according to claim 191, said annular opening is a mean annular opening to create a mean active heating zone surrounding said annular opening, said mean active heating zone to create a mean power load in said ablation zone.

197. The ablation probe tip according to claim 191, said annular opening being a mean annular opening for creating a mean active heating zone surrounding said annular opening, said mean active heating zone for creating mean maximum temperatures in said ablation zone.

198. The ablation probe tip according to claim 191, said annular opening being a long annular opening to create a long active heating zone surrounding said annular opening, said long active heating zone to create a low power load in said ablation zone.

199. The tip of the ablation probe according to claim 191, said annular opening being a long annular opening to create a long active heating zone surrounding said annular opening, said long active heating zone to create low maximum temperatures in said ablation zone.

200. The tip of the ablation probe according to claim 191, said coaxial antenna being a near-field antenna.

201. The tip of the ablation probe according to claim 191, said coaxial antenna is a near-field antenna, said ablation center is a stationary ablation center.

202. The tip of the ablation probe according to claim 191, said coaxial antenna is a near-field antenna, said near-field antenna prevents said ablation center from migrating upwards from said axis away from said insertion end.

203. The ablation probe tip according to claim 191 further comprises an annular heat transfer layer surrounding said coaxial antenna. MA / IZ / ZU¿Z / U1 Ul 1U 204. The ablation probe tip according to claim 191 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is between said annular heat transfer layer and said insertion end.

205. The ablation probe tip according to claim 191 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is located between said annular heat transfer layer and said insertion end, wherein said annular heat transfer layer prevents said ablation center from migrating upwards along said axis away from said insertion end.

206. The ablation probe tip according to claim 191, said ablation zone having a predetermined shape selected from the group consisting of oblate, spherical and oblong.

207. The ablation probe tip according to claim 191 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is located between said annular heat transfer layer and said insertion end, said ablation zone having a predetermined shape, said predetermined shape being determined by an opening offset, said opening offset being a distance between said ablation center and an annular edge of said annular heat transfer layer.

208. The ablation probe tip according to claim 191 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is between said annular heat transfer layer and said insertion end, said ablation zone having a predetermined shape, said predetermined shape being determined by an opening offset, said opening offset being a distance between said ablation center and an annular edge of said annular heat transfer layer, an oblate ablation zone having a relatively short opening offset, an oblong ablation zone having a relatively long opening offset, and a spherical ablation zone having an opening offset between said opening offsets of said oblate ablation zone and said oblong ablation zone.

209. The ablation probe tip according to claim 191 further comprises an annular heat transfer layer surrounding said coaxial antenna, said coaxial antenna further comprises an annular insulation layer surrounding said coaxial antenna in an annular manner, said annular heat transfer layer surrounding said annular insulation layer.

210. The ablation probe tip according to claim 191 further comprises an antenna end load positioned between said annular opening and said insertion end.

211. The ablation probe tip according to claim 191 further comprises an antenna end load positioned between said annular aperture and said insertion end, said antenna end load concentrating the energy density and increasing the power load.

212. The ablation probe tip according to claim 191 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is between said annular heat transfer layer and said insertion end, said annular heat transfer layer having high thermal conductivity and being electrically conductive.

213. The ablation probe tip according to claim 191, said coaxial antenna includes an inner conductor, an annular dielectric insulating layer surrounding said inner conductor, and an annular outer conductor surrounding said annular dielectric insulating layer, said annular opening exposing an annular ring of said annular dielectric insulating layer.

214. The ablation probe tip according to claim 191, said ablation probe tip being part of a surgical ablation kit including an ablation source, a handpiece, a stent, and a prescription.

215. The ablation probe tip according to claim 191, said ablation probe tip being part of a surgical ablation kit including an ablation source, a handpiece, a stent and a prescription, said prescription including at least one setting or parameter selected from the group consisting of: (a) ablation energy dose tolerances; (b) the energy level; and (c) the duration of energy delivery.

216. The ablation probe tip according to claim 191, said ablation probe tip for working in conjunction with a stent, said stent having a surgical guide, said surgical guide for guiding said ablation probe tip so that said ablation center is within the tissue.

217. The tip of the ablation probe according to claim 191, said coaxial antenna being a near-field reactive antenna.

218. The ablation probe tip according to claim 191 U11 a further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is located between said annular heat transfer layer and said insertion end, wherein said annular heat transfer layer blocks said ablation means from migrating upwards along said axis away from said insertion end, and said annular heat transfer layer permits thermal energy from said ablation zone to be conducted upwards along said axis away from said insertion end.

219. The ablation probe tip according to claim 191, said ablation probe tip being part of an ablation probe system having intra-operational maximum temperature control selected from the group consisting of: (a) passive cooling; (b) active cooling; and (c) a combination of passive and active cooling.

220. The ablation probe tip according to claim 191 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is located between said annular heat transfer layer and said insertion end, said annular heat transfer layer being turned off by the transfer of thermal energy from said annular heat transfer layer to the soft tissue surrounding said annular heat transfer layer.

221. The ablation probe tip according to claim 191, said ablation probe tip being part of an ablation probe system having intraoperative control of a volume of said ablation zone.

222. The ablation probe tip according to claim 191, said ablation probe tip being part of an ablation probe system having intraoperative control of a diameter of said ablation zone.

223. The ablation probe tip according to claim 191, said ablation probe tip, and said ablation means together enable at least one selected intraoperative control group consisting of: (a) position of said ablation zone; (b) shape of said ablation zone; (c) centering of said ablation zone; (d) maximum temperature of said ablation zone; (e) volume of said ablation zone; and (f) diameter of said ablation zone. U11 a 224. The ablation probe tip according to claim 191, said ablation probe tip being a microablation probe tip.

225. The ablation probe tip according to claim 191, said ablation probe tip being a microwave ablation probe tip.

226. The ablation probe tip according to claim 191, said ablation probe tip being a microwave ablation probe tip for receiving microwave energy from said ablation source as said ablation means, said microwave energy being delivered to said target tissue through said ablation probe tip.

227. The ablation probe tip according to claim 191, said ablation probe tip being a microwave ablation probe tip for receiving microwave energy from said ablation source as said ablation means, said ablation source providing microwave energy at frequencies ranging from 500 MHz to 20 GHz.

228. The ablation probe tip according to claim 191, said ablation probe tip being a radiofrequency ablation probe tip.

229. An ablation probe tip having a shaft with an insertion end, said ablation probe tip receiving ablation means from an ablation source, said ablation probe tip for ablating the target tissue, said ablation probe tip comprising: (a) said shaft including a coaxial antenna; (b) an annular aperture defined in at least one outer layer of said coaxial antenna towards said insertion end; (c) an ablation center located within said coaxial antenna and surrounded by said annular aperture, said ablation center being a focal region from which said ablation means radiate through said annular aperture to form an ablation zone; and (d) said ablation zone having a predetermined maximum temperature in said ablation zone.

230. The ablation probe tip according to claim 229, said ablation zone for selective ablation of said target tissue while mitigating damage to immediately adjacent collateral tissues.

231. The tip of the ablation probe according to claim 229, wherein at least part of said target tissue is destroyed by said ablation zone.

232. The ablation probe tip according to claim 229, said annular opening being a short annular opening to create a short active heating zone surrounding said annular opening, said short active heating zone to create a high power load in said ablation zone.

233. The ablation probe tip according to claim 229, said annular opening being a short annular opening to create a short active heating zone surrounding said annular opening, said short active heating zone to create high peak temperatures in said ablation zone.

234. The tip of the ablation probe according to claim 229, said annular opening is a mean annular opening to create a mean active heating zone surrounding said annular opening, said mean active heating zone to create a mean power load in said ablation zone.

235. The tip of the ablation probe according to claim 229, said annular opening is a mean annular opening for creating a mean active heating zone surrounding said annular opening, said mean active heating zone for creating mean maximum temperatures in said ablation zone.

236. The tip of the ablation probe according to claim 229, said annular opening is a long annular opening to create a long active heating zone surrounding said annular opening, said long active heating zone to create a low power load in said ablation zone.

237. The tip of the ablation probe according to claim 229, said annular opening is a long annular opening to create a long active heating zone surrounding said annular opening, said long active heating zone to create low maximum temperatures in said ablation zone.

238. The tip of the ablation probe according to claim 229, said coaxial antenna being a near-field antenna.

239. The tip of the ablation probe according to claim 229, said coaxial antenna is a near-field antenna, said ablation center is a stationary ablation center.

240. The tip of the ablation probe according to claim 229, said coaxial antenna is a near-field antenna, said near-field antenna prevents said ablation center from migrating upwards from said axis away from said insertion end.

241. The ablation probe tip according to claim 229 further comprises an annular heat transfer layer surrounding said coaxial antenna.

242. The ablation probe tip according to claim 229 further comprises an annular heat transfer layer surrounding said coaxial antenna and ivia / t / zuzz / ui ui iy is spaced from said insertion end, such that said annular opening is between said annular heat transfer layer and said insertion end.

243. The ablation probe tip according to claim 229 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is located between said annular heat transfer layer and said insertion end, wherein said annular heat transfer layer prevents said ablation center from migrating upwards along said axis away from said insertion end.

244. The ablation probe tip according to claim 229, said ablation zone having a predetermined shape selected from the group consisting of oblate, spherical and oblong.

245. The ablation probe tip according to claim 229 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is located between said annular heat transfer layer and said insertion end, said ablation zone having a predetermined shape, said predetermined shape being determined by an opening offset, said opening offset being a distance between said ablation center and an annular edge of said annular heat transfer layer.

246. The ablation probe tip according to claim 229 further comprises an annular heat transfer layer surrounding the coaxial antenna and spaced from the insertion end such that the annular opening is between the annular heat transfer layer and the insertion end, the ablation zone having a predetermined shape, the predetermined shape being determined by an opening offset, the opening offset being a distance between the ablation center and an annular edge of the annular heat transfer layer, an oblate ablation zone having a relatively short opening offset, an oblong ablation zone having a relatively long opening offset, and a spherical ablation zone having an opening offset between the opening offsets of the oblate ablation zone and the oblong ablation zone.

247. The ablation probe tip according to claim 229 further comprises an annular heat transfer layer surrounding said coaxial antenna, said coaxial antenna further comprises an annular insulation layer surrounding said coaxial antenna, said annular heat transfer layer surrounding said annular insulation layer.

248. The ablation probe tip according to claim 229 MLE / E / ZυZZZ / υΊ U11y 100 further comprises an antenna end load positioned between said annular opening and said insertion end.

249. The ablation probe tip according to claim 229 further comprises an antenna end load positioned between said annular opening and said insertion end, said antenna end load concentrating the energy density and increasing the power load.

250. The ablation probe tip according to claim 229 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is between said annular heat transfer layer and said insertion end, said annular heat transfer layer having high thermal conductivity and being electrically conductive.

251. The ablation probe tip according to claim 229, said coaxial antenna includes an inner conductor, an annular dielectric insulating layer surrounding said inner conductor, and an annular outer conductor surrounding said annular dielectric insulating layer, said annular opening exposing an annular ring of said annular dielectric insulating layer.

252. The ablation probe tip according to claim 229, said ablation probe tip being part of a surgical ablation kit including an ablation source, a handpiece, a stent, and a prescription.

253. The ablation probe tip according to claim 229, said ablation probe tip being part of a surgical ablation kit including an ablation source, a handpiece, a stent and a prescription, said prescription including at least one setting or parameter selected from the group consisting of: (a) ablation energy dose tolerances; (b) the energy level; and (c) the duration of energy delivery.

254. The ablation probe tip according to claim 229, said ablation probe tip for working in conjunction with a stent, said stent having a surgical guide, said surgical guide for guiding said ablation probe tip so that said ablation center is within the tissue.

255. The tip of the ablation probe according to claim 229, said coaxial antenna being a near-field reactive antenna.

256. The ablation probe tip according to claim 229 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is located between said annular heat transfer layer and said insertion end, wherein said annular heat transfer layer blocks said ablation means from migrating upwards along said axis away from said insertion end, and said annular heat transfer layer permits thermal energy from said ablation zone to be conducted upwards along said axis away from said insertion end.

257. The ablation probe tip according to claim 229, said ablation probe tip being part of an ablation probe system having intraoperative maximum temperature control selected from the group consisting of: (a) passive cooling; (b) active cooling; and (c) a combination of passive and active cooling.

258. The ablation probe tip according to claim 229 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is located between said annular heat transfer layer and said insertion end, said annular heat transfer layer being turned off by the transfer of thermal energy from said annular heat transfer layer to the soft tissue surrounding said annular heat transfer layer.

259. The ablation probe tip according to claim 229, said ablation probe tip being part of an ablation probe system having intraoperative control of a volume of said ablation zone.

260. The ablation probe tip according to claim 229, said ablation probe tip being part of an ablation probe system having intraoperative control of a diameter of said ablation zone.

261. The ablation probe tip according to claim 229, said ablation probe tip and said ablation means together enable at least one intraoperative control selected from the group consisting of: (a) position of said ablation zone; (b) shape of said ablation zone; (c) centering of said ablation zone; (d) maximum temperature of said ablation zone; (e) volume of said ablation zone; and (f) diameter of said ablation zone.

262. The ablation probe tip according to claim 229, said ablation probe tip being a microablation probe tip. ML / E / ZuZZ / u U11» 102 263. The ablation probe tip according to claim 229, said ablation probe tip being a microwave ablation probe tip.

264. The ablation probe tip according to claim 229, said ablation probe tip being a microwave ablation probe tip for receiving microwave energy from said ablation source as said ablation means, said microwave energy being delivered to said target tissue through said ablation probe tip.

265. The ablation probe tip according to claim 229, said ablation probe tip being a microwave ablation probe tip for receiving microwave energy from said ablation source as said ablation means, said ablation source providing microwave energy at frequencies ranging from 500 MHz to 20 GHz.

266. The ablation probe tip according to claim 229, said ablation probe tip being a radiofrequency ablation probe tip.

267. An ablation probe tip having a shaft with an insertion end, said ablation probe tip receiving ablation means from an ablation source, said ablation probe tip for ablating the target tissue, said ablation probe tip comprising: (a) said shaft including a coaxial antenna; (b) an annular aperture defined in at least one outer layer of said coaxial antenna towards said insertion end; (c) an ablation center located within said coaxial antenna and surrounded by said annular aperture, said ablation center being a focal region from which said ablation means radiate through said annular aperture to form an ablation zone; and (d) said ablation zone having an annular aperture and a power charge density in said ablation zone, said annular aperture and said power charge density being selected from the group consisting of: (i) a short annular aperture and a high power charge;(ii) a medium annular aperture and a medium power load; and (ii i) a large annular aperture and a low power load.; 268. The ablation probe tip according to claim 267, said ablation zone for selectively ablating said target tissue while mitigating damage to immediately adjacent collateral tissues.

269. The tip of the ablation probe according to claim 267, wherein at least part of said target tissue is destroyed by said ablation zone. 103 270. The ablation probe tip according to claim 267, said ablation zone having a maximum temperature in said ablation zone selected from the group consisting of: (a) said maximum temperature in said ablation zone is a high maximum temperature if said annular opening is a short annular opening; (b) said maximum temperature in said ablation zone is a medium maximum temperature if said annular opening is a medium annular opening; and (c) said maximum temperature in said ablation zone is a low maximum temperature if said annular opening is a long annular opening.

271. The tip of the ablation probe according to claim 267, said coaxial antenna being a near-field antenna.

272. The tip of the ablation probe according to claim 267, said coaxial antenna is a near-field antenna, said ablation center is a stationary ablation center.

273. The tip of the ablation probe according to claim 267, said coaxial antenna is a near-field antenna, said near-field antenna prevents said ablation center from migrating upwards from said axis away from said insertion end.

274. The ablation probe tip according to claim 267 further comprises an annular heat transfer layer surrounding said coaxial antenna.

275. The ablation probe tip according to claim 267 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is between said annular heat transfer layer and said insertion end.

276. The ablation probe tip according to claim 267 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is between said annular heat transfer layer and said insertion end, wherein said annular heat transfer layer prevents said ablation center from migrating upwards along said axis away from said insertion end.

277. The ablation probe tip according to claim 267, said ablation zone having a predetermined shape selected from the group consisting of oblate, spherical and oblong.

278. The ablation probe tip according to claim 267 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is located between said annular heat transfer layer and said insertion end, said ablation zone having a predetermined shape, said predetermined shape determined by an opening offset, said opening offset being a distance between said ablation center and an annular edge of said annular heat transfer layer.

279. The ablation probe tip according to claim 267 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is between said annular heat transfer layer and said insertion end, said ablation zone having a predetermined shape, said predetermined shape being determined by an opening offset, said opening offset being a distance between said ablation center and an annular edge of said annular heat transfer layer, an oblate ablation zone having a relatively short opening offset, an oblong ablation zone having a relatively long opening offset, and a spherical ablation zone having an opening offset between said opening offsets of said oblate ablation zone and said oblong ablation zone.

280. The ablation probe tip according to claim 267 further comprises an annular heat transfer layer surrounding said coaxial antenna, said coaxial antenna further comprises an annular insulation layer surrounding said coaxial antenna, said annular heat transfer layer surrounding said annular insulation layer.

281. The ablation probe tip according to claim 267 further comprises an antenna end load positioned between said annular opening and said insertion end.

282. The ablation probe tip according to claim 267 further comprises an antenna end load positioned between said annular opening and said insertion end, said antenna end load concentrating the energy density and increasing the power load.

283. The ablation probe tip according to claim 267 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is between said annular heat transfer layer and said insertion end, said annular heat transfer layer having high thermal conductivity and being electrically conductive.

284. The ablation probe tip according to claim 267, said coaxial antenna includes an inner conductor, an annular dielectric insulating layer surrounding said inner conductor, and an annular outer conductor surrounding said annular dielectric insulating layer, said annular opening exposing an annular ring of said annular dielectric insulating layer.

285. The ablation probe tip according to claim 267, said ablation probe tip being part of a surgical ablation kit including an ablation source, a handpiece, a stent, and a prescription.

286. The ablation probe tip according to claim 267, said ablation probe tip being part of a surgical ablation kit including an ablation source, a handpiece, a stent and a prescription, said prescription including at least one setting or parameter selected from the group consisting of: (a) ablation energy dose tolerances; (b) the energy level; and (c) the duration of energy delivery.

287. The ablation probe tip according to claim 267, said ablation probe tip for working in conjunction with a stent, said stent having a surgical guide, said surgical guide for guiding said ablation probe tip so that said ablation center is within the tissue.

288. The tip of the ablation probe according to claim 267, said coaxial antenna being a near-field reactive antenna.

289. The ablation probe tip according to claim 267 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is located between said annular heat transfer layer and said insertion end, wherein said annular heat transfer layer blocks said ablation means from migrating upwards along said axis away from said insertion end, and said annular heat transfer layer permits thermal energy from said ablation zone to be conducted upwards along said axis away from said insertion end.

290. The ablation probe tip according to claim 267, said ablation probe tip being part of an ablation probe system having intra-operational maximum temperature control selected from the group consisting of: (a) passive cooling; (b) active cooling; and (c) a combination of passive and active cooling.

291. The ablation probe tip according to claim 267 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is located between said annular heat transfer layer and said insertion end, said annular heat transfer layer being turned off by the transfer of thermal energy from said annular heat transfer layer to the soft tissue surrounding said annular heat transfer layer.

292. The ablation probe tip according to claim 267, said ablation probe tip being part of an ablation probe system having intraoperative control of a volume of said ablation zone.

293. The ablation probe tip according to claim 267, said ablation probe tip being part of an ablation probe system having intraoperative control of a diameter of said ablation zone.

294. The ablation probe tip according to claim 267, said ablation probe tip and said ablation means together enable at least one selected intraoperative control of the group consisting of: (a) position of said ablation zone; (b) shape of said ablation zone; (c) centering of said ablation zone; (d) maximum temperature of said ablation zone; (e) volume of said ablation zone; and (f) diameter of said ablation zone.

295. The ablation probe tip according to claim 7267, said ablation probe tip being a microablation probe tip.

296. The ablation probe tip according to claim 267, said ablation probe tip being a microwave ablation probe tip.

297. The ablation probe tip according to claim 267, said ablation probe tip being a microwave ablation probe tip for receiving microwave energy from said ablation source as said ablation means, said microwave energy being delivered to said target tissue through said ablation probe tip.

298. The ablation probe tip according to claim 267, said ablation probe tip being a microwave ablation probe tip for receiving microwave energy from said ablation source as said ablation means, said ablation source providing microwave energy at frequencies ranging from 500 MHz to 20 GHz.

299. The ablation probe tip according to claim 267, said ablation probe tip being a radiofrequency ablation probe tip. ML / E / ZuZZ / uU11» 107 300. An ablation probe tip having a shaft with an insertion end, said ablation probe tip receiving ablation means from an ablation source, said ablation probe tip for ablating the target tissue, said ablation probe tip comprising: (a) said shaft including a coaxial antenna; (b) an annular aperture defined in at least one outer layer of said coaxial antenna towards said insertion end; (c) an ablation center located within said coaxial antenna and surrounded by said annular aperture, said ablation center being a focal region from which said ablation means radiate through said annular aperture to form an ablation zone; and (d) said ablation zone having an annular aperture and a peak temperature in said ablation zone, said annular aperture and said peak temperature being selected from the group consisting of: (i) a short annular aperture and a high peak temperature;(ii) a medium annular aperture and a medium peak temperature; and (ii i) a large annular aperture and a low peak temperature.; 301. The ablation probe tip according to claim 300, said ablation zone for selective ablation of said target tissue while mitigating damage to immediately adjacent collateral tissues.

302. The tip of the ablation probe according to claim 300, wherein at least part of said target tissue is destroyed by said ablation zone.

303. The tip of the ablation probe according to claim 300, said coaxial antenna being a near-field antenna.

304. The tip of the ablation probe according to claim 300, said coaxial antenna is a near-field antenna, said ablation center is a stationary ablation center.

305. The tip of the ablation probe according to claim 300, said coaxial antenna is a near-field antenna, said near-field antenna prevents said ablation center from migrating upwards from said axis away from said insertion end.

306. The ablation probe tip according to claim 300 further comprises an annular heat transfer layer surrounding said coaxial antenna.

307. The ablation probe tip according to claim 300 further comprises an annular heat transfer layer surrounding said coaxial antenna and separated from said insertion end, such that said annular opening is between ML / IZ / ZυZZZ / υΊ UII and 108 said annular heat transfer layer and said insertion end.

308. The ablation probe tip according to claim 300 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is located between said annular heat transfer layer and said insertion end, wherein said annular heat transfer layer prevents said ablation center from migrating upwards along said axis away from said insertion end.

309. The ablation probe tip according to claim 300, said ablation zone having a predetermined shape selected from the group consisting of oblate, spherical and oblong.

310. The ablation probe tip according to claim 300 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is located between said annular heat transfer layer and said insertion end, said ablation zone having a predetermined shape, said predetermined shape being determined by an opening offset, said opening offset being a distance between said ablation center and an annular edge of said annular heat transfer layer.

311. The ablation probe tip according to claim 300 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end such that said annular opening is between said annular heat transfer layer and said insertion end, said ablation zone having a predetermined shape, said predetermined shape determined by an opening offset, said opening offset being a distance between said ablation center and an annular edge of said annular heat transfer layer, an oblate ablation zone having a relatively short opening offset, an oblong ablation zone having a relatively long opening offset, and a spherical ablation zone having an opening offset between said opening offsets of said oblate ablation zone and said oblong ablation zone.

312. The ablation probe tip according to claim 300 further comprises an annular heat transfer layer surrounding said coaxial antenna, said coaxial antenna further comprises an annular insulation layer surrounding said coaxial antenna, said annular heat transfer layer surrounding said annular insulation layer.

313. The ablation probe tip according to claim 300 further comprises an antenna end load positioned between said annular opening and said MLE / E / ZuZZ / u / U11y 109 insertion end.

314. The ablation probe tip according to claim 300 further comprises an antenna end load positioned between said annular opening and said insertion end, said antenna end load concentrating the energy density and increasing the power load.

315. The ablation probe tip according to claim 300 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is between said annular heat transfer layer and said insertion end, said annular heat transfer layer having high thermal conductivity and being electrically conductive.

316. The ablation probe tip according to claim 300, said coaxial antenna includes an inner conductor, an annular dielectric insulating layer surrounding said inner conductor, and an annular outer conductor surrounding said annular dielectric insulating layer, said annular opening exposing an annular ring of said annular dielectric insulating layer.

317. The ablation probe tip according to claim 300, said ablation probe tip being part of a surgical ablation kit including an ablation source, a handpiece, a stent, and a prescription.

318. The ablation probe tip according to claim 300, said ablation probe tip being part of a surgical ablation kit including an ablation source, a handpiece, a stent and a prescription, said prescription including at least one setting or parameter selected from the group consisting of: (a) ablation energy dose tolerances; (b) the energy level; and (c) the duration of energy delivery.

319. The ablation probe tip according to claim 300, said ablation probe tip for working in conjunction with a stent, said stent having a surgical guide, said surgical guide for guiding said ablation probe tip so that said ablation center is within the tissue.

320. The tip of the ablation probe according to claim 300, said coaxial antenna being a near-field reactive antenna.

321. The ablation probe tip according to claim 300 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is located between said annular heat transfer layer and said insertion end, wherein said annular heat transfer layer blocks said ablation means from migrating upwards along said axis away from said insertion end, and said annular heat transfer layer permits thermal energy from said ablation zone to be conducted upwards along said axis away from said insertion end.

322. The ablation probe tip according to claim 300, said ablation probe tip being part of an ablation probe system having intra-operational maximum temperature control selected from the group consisting of: (a) Passive cooling; (b) active cooling; and (c) a combination of passive and active cooling.

323. The ablation probe tip according to claim 300 further comprises an annular heat transfer layer surrounding said coaxial antenna and spaced from said insertion end, such that said annular opening is located between said annular heat transfer layer and said insertion end, said annular heat transfer layer being turned off by the transfer of thermal energy from said annular heat transfer layer to the soft tissue surrounding said annular heat transfer layer.

324. The ablation probe tip according to claim 300, said ablation probe tip being part of an ablation probe system having intraoperative control of a volume of said ablation zone.

325. The ablation probe tip according to claim 300, said ablation probe tip being part of an ablation probe system having intraoperative control of a diameter of said ablation zone.

326. The ablation probe tip according to claim 300, said ablation probe tip and said ablation means together enable at least one selected intraoperative control of the group consisting of: (a) position of said ablation zone; (b) shape of said ablation zone; (c) centering of said ablation zone; (d) maximum temperature of said ablation zone; (e) volume of said ablation zone; and (f) diameter of said ablation zone.

327. The ablation probe tip according to claim 300, said ablation probe tip being a microablation probe tip.

328. The ablation probe tip according to claim 300, MLE / E / ZUZZ / Ul Ul 1y 111, said ablation probe tip being a microwave ablation probe tip.

329. The ablation probe tip according to claim 300, said ablation probe tip being a microwave ablation probe tip for receiving microwave energy from said ablation source as said ablation means, said microwave energy being delivered to said target tissue through said ablation probe tip.

330. The ablation probe tip according to claim 300, said ablation probe tip being a microwave ablation probe tip for receiving microwave energy from said ablation source as said ablation means, said ablation source providing microwave energy at frequencies ranging from 500 MHz to 20 GHz.

331. The ablation probe tip according to claim 300, said ablation probe tip being a radiofrequency ablation probe tip.

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