Method and Apparatus for Treating Female Urinary Incontinence and Fecal Incontinence

Abstract

A device and method for treating female urinary incontinence and also for treating fecal incontinence are presented. A fractional RF grid array is used to heat target tissue to a temperature of about 40-45? C. for a specified period of time, thus stimulating fibroblasts to produce type 1 collagen preferably without producing significant amounts of type 3 collagen. The device includes a temperature sensor and a control circuit to maintain the desired temperature of the target tissue and avoid overheating. Target tissue includes tissue in and around the urethra, and in and around the anus including the perineum. The wand to which the RF grid array is mounted has visible gradations on it so that the user can treat one area at a time, then reliably move the grid array to the next adjacent area even though the grid array is hidden from view inside a portion of the body. The device can also be used for vaginoplasty.

Claims

1. A method of tightening target epithelium within a patient comprising: raising the temperature of said target epithelium to greater than 40? C.; wherein said target epithelium comprises at least one of vaginal epithelium and perineum epithelium.

2. The method of claim 1 wherein said target epithelium is raised to a temperature of between 40? C. and a maximum of 45? C.

3. The method of claim 1 wherein said target epithelium is raised to a temperature of between 43? C. and a maximum of 44? C.

4. The method of claim 17 wherein said target epithelium comprises vaginal epithelium surrounding a urethral opening.

5. The method of claim 4 wherein said target epithelium comprises vaginal epithelium and does not include tissue within a hymenal ring of the patient.

6. The method of claim 1 wherein said target epithelium comprises labial epithelium surrounding a urethral opening.

7. The method of claim 1 wherein said target epithelium comprises perineum epithelium.

8. The method of claim 7 wherein said raising of the temperature comprises heating using a fractional RF array to delivery radiofrequency energy to target tissue.

9. The method of claim 8 wherein said fractional RF array is distributed over an area of at least 1 cm.sup.2.

10. The method of claim 9 further comprising monitoring electrical impedance from the RF array through the patient to indirectly monitor temperature of the target tissue, and adjusting a power level of the RF energy in order to achieve a desired target temperature within said target epithelium.

11. The method of claim 10 wherein the RF energy is adjusted to maintain a regulated dose of RF energy.

12. The method of claim 1 wherein the method constitutes a method of treating pelvic pain in the patient, and the target.

13. The method of claim 12 wherein the pelvic pain comprises dyspareunia.

14. The method of claim 1 wherein the target epithelium comprises vaginal epithelium, and the method constitutes a method of increasing vaginal lubrication in the patient.

15. A method of treating urinary incontinence in a female patient, the patient having a urethra and urethral opening, the method comprising: raising the temperature of target tissue to above 40? C., wherein the target tissue comprises at least one of: tissue surrounding the urethral opening; and tissue inside the urethra.

16. The method of claim 15 wherein said temperature is raised to between 40? C. and a maximum of 45? C.

17. The method of claim 15 wherein said target tissue is tissue inside the urethra.

18. The method of claim 15 wherein said raising of the temperature comprises heating using a fraction RF array to delivery radiofrequency energy to the target tissue.

19. The method of claim 18 wherein said fractional RF array has at least 9 electrodes distributed over an area of at least 1 cm.sup.2.

20. A method of treating fecal incontinence in a patent, the patient having an anus, the anus including anal tissue, the method comprising: raising the temperature of said anal tissue to greater than 40? C.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

[0012] FIG. 1 is a perspective view of an illustrative embodiment of the medical device of the present invention.

[0013] FIG. 2 is a closeup of the electrode of the medical device of FIG. 1.

[0014] FIG. 3 is a closeup of the proximal end of the medical device of FIG. 1 showing the electrical contacts thereof.

[0015] FIG. 4 is a side view of the electrode of the medical device of FIG. 1.

[0016] FIG. 5 is a simplified diagram of the pelvic region of a female patient, illustrating exterior areas that are suitable for treatment according to the present invention.

[0017] FIG. 6 is a graph of patient data for vaginal laxity treatment according to the present invention.

[0018] FIG. 7 is a graph of patient data for urologic distress treatment according to the present invention.

[0019] FIG. 8 is a graph of patient data for urologic distress treatment according to the present invention.

[0020] FIG. 9 is a graph of patient data for sexual dysfunction treatment according to the present invention.

[0021] FIG. 10 is a graph of patient data for sexual desire treatment according to the present invention.

[0022] FIG. 11 is a graph of patient data for sexual arousal treatment according to the present invention.

[0023] FIG. 12 is a graph of patient data for sexual satisfaction treatment according to the present invention.

[0024] FIG. 13 is another graph of patient data for sexual satisfaction treatment according to the present invention.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0025] 1. The Device

[0026] FIG. 1 is a perspective view of an illustrative embodiment of the medical device 10 of the present invention. The device 10 includes a wand portion 12 having a smoothly rounded proximal end 30 and an electrode (e.g., a fractional RF array) 20, which may be a grid or plate, and a distal end 30. At a proximal end 32 of the wand portion 12 is a generally conical section 34 having a thread 36 so that the electrical cable which supplies the input electrical signal to the electrode 20 can be securely fastened to wand portion 12. For definitional purposes, the proximal end 32 is the end at which the doctor or other treating professional holds the device, and the distal end 30 is the end that is opposite the distal end 32. The wand portion 12 is approximately 14.5 cm long and approximately 2.5 cm wide in one embodiment. More generally, the wand portion can be approximately 8-20 cm long and approximately 1.5-4 cm wide.

[0027] The wand portion 12 has a number of visible longitudinal gradations 16 marked on it, as well as a number of visible circumferential gradations 18 marked on it, whose use will be explained later. The circumferential gradations 18 are spaced at regular intervals that approximately equal the transverse width of the electrode 20. In the illustrative embodiment there are 5 circumferential gradations 18 spaced equally around the circumference of the device (which can be marked 0 thru 4 or in some other suitable manner).

[0028] The longitudinal gradations 16 also can be marked at regular intervals. The longitudinal gradations are spaced at regular intervals that approximately equal the longitudinal length of the electrode 20. In the illustrative embodiment the gradations 16, 18 are grooves in the surface of wand portion 12, but could be printed or otherwise marked.

[0029] As mentioned above, at the proximal end 32 of the device 10, the conical portion 34 has a thread 36 near the far end. The thread 36 allows an electrical connection cable (not shown in FIG. 1) to be securely attached via a freely rotating threaded ring on the cable that mates with the thread 36 thereby securing the cable to the device 10. Such mating threads to secure electrical connections are well known.

[0030] FIG. 2 is a closeup of the electrode 20 of the medical device 10 of FIG. 1. The electrode 20 may take the form of a screen with commonly connected electrode elements 22 with spaces 24 between the electrode elements 22. In use, the electrode elements 22 within the electrode 20 do not directly touch the patient's skin or other target tissue. That is, the electrode elements 22 are not placed in direct electrical contact with the skin. Rather, the electrode elements 22 are covered by an electrical insulator 26 (see FIG. 4), preferably a dielectric and non-toxic, high temperature resistant, medical grade material such as polyimide (e.g., KAPTON?), such that direct electrical current does not pass from the electrodes to the target tissue. The electrode 20 emits electromagnetic radiation, preferably in the RF spectrum such as approximately 1 MHZ, 2 MHz, or 6 MHz, which electromagnetic radiation causes heating within the target tissue. Additionally, alternating current (AC) is capacitively coupled between the electrode elements 22 within the electrode 20 and the target tissue, also heating the target tissue. Because the electrodes are monopolar, the device is used with a metal ground plate 50 (see FIG. 5) that is applied to the patient such as on the patient's thigh or buttock during treatment and in direct electrical contact therewith. Ground potential is provided to the ground plate 50 via a ground lead wire 52 (see FIG. 5).

[0031] Because the energy that is applied to the electrode 20 is capacitively coupled into the target tissue rather than electrical current flowing from electrode 20 to the tissue, the electrode elements 22 together act as a capacitor charge plate, with the electrical charge spreading out uniformly over the entire plate, and the energy being transmitted to the target tissue via electromagnetic emission in the RF spectrum. This creates a much more uniform application of RF energy to the target tissue over the entire area of electrode 20. In contrast, if electrical current were to flow from the electrode 20 to the target tissue, the current would have a tendency to flow through the path of least resistance, with the result being that the current flow would occur more or less at a single point. Because the energy is spread out and transmitted uniformly, the doctor can hold the electrode 20 over a single spot on the tissue, apply one or more metered pulses of energy, and know exactly how much energy has been applied to the target tissue and know that the energy was applied uniformly over the area of the electrode 20.

[0032] This allows a system that includes the device 10 and a controller to monitor the tissue that is being treated by using impedance sensing/feedback, and adjust the amount of energy being delivered during the actual treatment.

[0033] In contrast, other systems that use impedance monitoring are actually monitoring the impedance of tissue that has already been treated. Such systems can monitor an average impedance within the tissue, but they cannot compensate and adjust the energy for the tissue that is about to be treated.

[0034] A system based on the present invention can monitor impedance and adjust the power level several times during a pulse. For example, such a system can monitor the impedance, adjust the energy, deliver the energy, then monitor the impedance again, and adjust the energy. The system can therefore fine-tune the amount of energy delivered into tissue so that all tissue in the treated area receives the same amount of energy and receives the same amount of heat. Thus, the system effectively acts like a dermal thermostat. As energy is delivered to tissue, the tissue's characteristics change. The resistance of human tissue decreases with increasing temperature.

[0035] For rapidly moving electrodes as used in some prior art treatment methods, it is difficult to adjust the amount of energy delivered based on temperature of the target tissue. Such systems commonly employ constant voltage or constant current and as the electrodes move over tissue, tissue that has been heated before will have less resistance and hence will absorb more energy than tissue that has not been treated, increasingly channeling the electrical current through the spots that have already been treated and away from the areas that have not been treated. The tissue will develop hotter and hotter hot spots and colder and colder cold spots, but on the average the temperature sensor will measure a uniform temperature because the doctor or other treating professional is moving the probe rapidly over tissue and the temperature monitors are averaging out the inconsistencies.

[0036] In contrast, by employing a feedback control loop, a system which uses the electrode 20 can adjust the energy for the optimum amount to be delivered to the target tissue, resulting in a more comfortable and uniform treatment.

[0037] In the illustrative embodiment, the device 10 uses monopolar electrodes together with a ground plate 50 as discussed herein. Alternatively, the device could use bipolar, tripolar, qudrapolar, tetrapolar, or any combination of electrodes including fractional bipolar electrodes.

[0038] Preferably the device includes a screen electrode or grid electrodes (e.g., 9 spaced commonly connected electrodes 22) distributed over an area of at least 1 cm.sup.2, and more preferably a screen electrode of grid electrodes (e.g., 25 spaced commonly connected electrodes 22) distributed over an area of at least 2 cm.sup.2.

[0039] In the exemplary embodiment, the electrode 20 is a grid of monopolar microelectrodes that is sometimes called a grid fractional applicator. Such an electrode is currently manufactured by Jesisys Medical, Inc. of Korea (Jesisy Medical) and designated by model number KT-15 for a 15 mm?15 mm grid array. The KT-15 grid array uses an array of 9?9 commonly connected electrodes potted in a polymer for a total of 81 fractional electrodes over an area of approximately 2.25 cm. As used herein, the grid acts as a plate except at the immediate surface where the field concentrated at the grid wires leaves a fractional grid thermal pattern in the epidermis to cause fractional resurfacing of the epidermis.

[0040] FIG. 3 is a closeup of the proximal end 32 of the medical device of FIG. 1 showing electrical contacts 38 and 39 thereof. An electrical cable leading to a control unit (not shown in FIG. 1) including a pulse generator physically and electrically mates with this end of the device.

[0041] FIG. 4 is a side view of the electrode 20 of the medical device 10 of FIG. 1. As shown, the electrode 20 may include electrode elements 22 (e.g., a metal screen electrode which acts as a plate electrode) covered by the electrical insulator 26. In addition, a conductor 54 provides an electrical connection to a signal generator (not shown in FIG. 4).

[0042] The electrode 20 and device 10 of the present invention differ markedly from prior RF treatment devices such as the one described in U.S. Pat. No. 8,540,705 to Mehta and sold by Syneron Medical Ltd. aka Syneron Candela, in that those prior devices feature an array of microneedles that penetrate the skin and thus deliver RF energy subcutaneously, delivering the energy through the sharp end point of the needle, and to a ground pad applied to the patient. The electrical current of those devices flow through the well-defined tip of the needle into tissue, flowing primarily through the path of least electrical resistance from the tip of the needle to a sharp edge or protrusion of corner of the ground pad, providing imprecise electrocautery.

[0043] The electrode 20 and device 10 also provide a more uniform treatment field than prior devices such as disclosed in U.S. Pat. No. 8,961,511 to Palmer and corresponding devices sold by Viveve, Inc. In those devices electrical current flows from the electrodes through the target tissue and to a ground plate. Again, the electrical current will choose the path of least resistance, such that the electrocautery is more localized than desired. Thus, the doctor must move those devices around rapidly over the target tissue to prevent burning. When moving a wand around rapidly over a surface to treat the surface uniformly the doctor is unable to determine fluence at any point in the tissue, and it can be difficult for the doctor to obtain consistent results.

[0044] The exemplary device 10 also has an electrical impedance sensor or monitor for indirectly sensing the temperature of the tissue to which the device is applied, by measuring tissue impedance and using known relationships between tissue impedance and tissue temperature. The device 10 includes a control circuit operatively connected to the impedance monitor and the electrode 20 to prevent the tissue from being heated beyond a predetermined maximum temperature. The impedance monitor indirectly senses the tissue temperature and provides feedback to a power control circuit. The relationship between skin temperature and electrical impedance is well known. See for example, R. Gudivaka et al, Effect of Skin Temperature on Multifrequency Bioelectrical Impedance Analysis, Journal of Applied Physiology, August 1996, 81(2): 838-45 which is hereby incorporated by reference in its entirety. Current through the electrode 20 and into the human body quickly spreads out in the body providing a wide electrical path, such that the impedance of the heated tissue immediately adjacent the electrode 20 constitutes the major contributor to the total impedance sensed, and thus the temperature of that heated tissue can be accurately calculated.

[0045] The electrode 20 (e.g., the model KT-15 RF grid array) indirectly measures temperature of the target tissue by measuring electrical impedance through the body including through the target heated tissue to which it is applied. The impedance monitor provides feedback to the control circuit which can actively adjust the RF power applied to maintain a controlled energy dose for a constant temperature rise. A control circuit for monitoring the impedance and for adjusting the power applied to the electrode 20 to achieve the desired temperature of the target tissue may be located in an external unit that generates the electrical input to the device 10 and hence the electrode 20. The control circuit may apply one or multiple pulses of energy at spaced intervals such as regular intervals to first bring the target tissue to the target temperature and then to hold it at the target temperature for the desired time. The control circuit may therefore apply energy at a higher average power for a short time duration initially to quickly bring the target tissue to the desired temperature and then reduce the average power to maintain the target tissue at that temperature for the desired time. The control circuit may adjust any or more of the following parameters to achieve the desired treatment profile: instantaneous power, On time, and duty cycle.

[0046] The device could use means other than RF energy for raising the temperature of the target tissue including but not limited to direct heating, and electromagnetic waves within the microwave spectrum or other frequency spectrum.

[0047] It is preferred that the temperature of the target tissue during treatment be within the range of 40? C.-48? C., and more preferably within the range of between 40? C. and a maximum of 45? C., and more preferably still to within the range of 43? C.-44? C. Above 45? C. the cells begin to burn, resulting in production of too much type 3 collagen which is scar tissue. Keeping the temperature of the target temperature to within the range of about 40? C. to 45? C. stimulates the fibroblasts and thus stimulates the production of mostly type 1 collagen which is has better elasticity than type 3 collagen, and results in only partial denaturation of the existing collagen. RF energy produces heat which promotes neo-collagenesis, denaturation of collagen cross-links, activation of wound healing pathways, contraction of collagen, and increase in collagen fibril size. The phenomenon of thermal contraction of collagen begins with a denaturation of the triple helix of the collagen molecule. Partial denaturation of collagen tissue results in a contraction of the collagen-rich spaces and provides a tightening effect on the overlaying tissue.

[0048] Heat is the result of RF waves experiencing impedance as the RF waves traverse the tissue bed. As the RF waves permeate a tissue layer, electric fields are induced across the tissue, and ions found within that layer deliver or carry an electrical current. This, in turn, increases the kinetic activity of the ions. Increased ion kinetics and oscillations engenders resistive heating in tissue called thermogenesis heating. The degree of heating is calculable via the Specific Absorption Rate (SAR) equation, which assesses local electrical conductivity and magnitude of local electric current density generated around the electrode:

[00001]$\begin{array}{cc}\mathrm{SAR}=\frac{?}{?}.Math.{.Math.E.Math.}^2=\frac{1}{?.Math..Math.?}.Math.{.Math.J.Math.}^2& \mathrm{EQUATION}.Math..Math.1\end{array}$

[0049] The therapeutic benefit is localized thermogenesis heating. The electric field strength generated is capable of heating tissue in close proximity to the electrode. Dispersion of the electric field causes decreasing energy deposition away from the surface of the electrode. With proper controls, generating the ideal thermal endpoint will occur close to the electrode, affecting only a specific tissue.

[0050] Grid fractional radio frequency energy creates thermal grid shapes on the surface and a uniform thermal zone in tissue during RF emission. Regulated RF current is adjusted via power control to match the desired impedance, which corresponds via known relationships to tissue temperature. Power absorbed equals the square of the electrical current delivered to by the radiofrequency electrode times the tissue impedance. The tissue impedance will be monitored, and the power will be adjusted to ensure that the proper current is delivered to achieve the desired tissue impedance. In summary, feedback from the impedance sensor is monitored by the control system, and power is adjusted to maintain the therapeutic energy deposition and resultant temperature rise in tissue. Altogether, with these proper controls in place, selective thermogenesis heating serves as a viable treatment for numerous medical conditions.

[0051] The variables involved in changing collagen relate to temperature delivered to a specific area of tissue over a certain time. The maximal shrinkage of collagen tightening before the tissue becomes too weak is 15-20% (see Wall, M S, et al., J Shoulder Elbow Surg.; 1999 July-August; 8(4):339-44). The shrinkage of collagen is related to time and the amount of energy applied.

[0052] Preferably the target tissue is heated to the preferred temperature of 43? C.-44? C. for a specified exposure time. This can be accomplished by applying various waveform profiles to the electrode 20.

[0053] FIG. 5 is a simplified diagram of the pelvic region of a female patient 100, illustrating exterior areas that are suitable for treatment according to the present invention.

[0054] For treating female urinary incontinence, the target tissue includes: vaginal epithelium in the tissue 107 surrounding the urethral opening 106 but not including tissue within the hymenal ring 104; labial epithelium including of the labia minora 120 and labia majora 122 surrounding the urethral opening 106, and anywhere outside the pelvic floor; and epithelium in the perineum 140. The volume of blood flow within this area is sufficiently high that the electrode 20 can be applied to one area to effectively heat local surrounding tissue that receives the flow of heated blood. Collagen production can thus be stimulated in a surrounding adjacent area other than the area that is immediately underneath or adjacent to the electrode 20.

[0055] Also visible in the figure are the vagina 102, clitoris 108, Hart line 110, anus 130, and anal tissue 132.

[0056] The marked gradations 16, 18 on the device as seen in FIG. 1 assist the treating professional in achieving full coverage of the target area without overlap, when the area being treated is within the vagina or within the anus. The longitudinal gradations 16 marked on the device can be used to ensure that the electrode 20 is placed at the desired depths, and the circumferentially marked gradations 18 allow the treating professional to achieve the treatment desired circumferentially (e.g., within the range of 0?-360? of arc, or only a narrower arc, such as 30?-330? of arc) to avoid the clitoral area, at a specified depth, obtaining full coverage of the target tissue and without overlap. For example, a treating professional might insert the device up to the first marked longitudinal mark 16, apply energy to the device for a first time period to treat the area of tissue that is touching the electrode 20, rotate the device by one circumferential gradation 18, then apply energy to the device for the same time period, and so on until energy has been applied at that depth around the entire 0?-360? of arc. Then the treating professional inserts the device to the next longitudinal mark 16, and repeats the treatment within the circumferential range of 0?-360?. In this way the treating professional applies the electrode 20 to each portion of the treatment area sequentially and achieves full coverage of the target tissue but without overlap, which could cause overexposure and therefore less than ideal response within the target tissue or even burning. In this way the doctor can assure uniform treatment of the entire target area within the patient's vagina, and to a predetermined depth, without having to see the electrode 20 or the tissue to which it is applied. The markings therefore eliminate the guesswork that was necessary with some prior art devices for treating inside body cavities, in which the devices were intended to be swirled rapidly within the body cavity to ensure uniform treatment, and in which it was difficult for the doctor to achieve uniform treatment of the target tissue.

[0057] 2. Treating Urinary Incontinence

[0058] The device 10 may be applied to treat female urinary incontinence by tightening vaginal epithelium around the urethral opening 106, particularly urinary stress incontinence for which common contributing causes include a weakened urethral sphincter and weakened pelvic floor muscles. The etiology of urinary incontinence is multifactorial. Stretching, tearing and separating of the pelvic floor support tissue during childbirth along with other traumatic conditions of chronic coughing, weight bearing and collagen vascular disorders increase the risk of incontinence and pelvic floor prolapse. Other causes include The Genitourinary Syndrome of Menopause (GSM) which is a progressive devastating condition from the reduction of estrogen and blood flow on the urogenital tissue (Portman, 2014, Maturutas). The clinical findings of pale pink vaginal epithelium with flattened dry rugae and associated urinary symptoms of urgency, frequency, incontinence, dysuria, dryness, burning, pain, sexual dysfunction affect up to 50% of menopausal women.

[0059] FIGS. 6 and 7 illustrates preliminary data for 14 patients from a clinical trial (NTC03280446 Clinicaltrials.gov). The scores prior to treatment (PRE TX) and after treatment (POST TX) reveal a statically significant improvement on the Urological Distress Inventory (UDI) (FIG. 6), the Incontinence Impact Questionaire (IIQ), and the Urinary Quality of Life Questionaire (QOL) (FIG. 7). In the figures, the parameter p relates to the statistical significance (e.g., with p<0.05 indicating statistical significance). The Incontinence QOL Questionaire states: If you were to spend the rest of your like with your urinary condition just the way it is now, how would you feel about that? Circle the number that best reflects your feelings about your urinary problem. Scores range from 0 to 10, indicating pleased (low scores e.g., 0), indifferent (medium score, e.g., 5), or terrible (high score, e.g., 10).

[0060] The treatment device 10 of FIGS. 1-3 can be used to treat the areas discussed above. Additionally, a different and much smaller treatment wand could be used to treat tissue inside the urethra itself. Applying the treatment inside the urethra stimulates the production of collagen there and hence strengthens and tightens the urethral opening.

[0061] Although it is believed that the method and device of the present invention will be most effective for treating urinary stress incontinence, it is believe that the method and device will also have efficacy in treating urinary urge incontinence.

[0062] The application of radiofrequency to tissue surrounding the urethra and rectal sphincter tightens the supporting tissue by creating new extracellular collagen and elastin matrix. The resulting tighter and better-recoiling tissue will increase the tone and pressure, and coaptic ability within the urethra and rectal sphincter. As a result the patient will experience less incontinence both at rest and with contraction of the pelvic floor.

[0063] Some techniques for tissue tightening that have been proposed by others use high temperatures such as up to 85? C. and rely heavily on denaturation of existing collagen within the tissue. (see Wall mentioned above). Although denaturation of the collagen triple helix does result in shrinkage of the tissue, it also produces the undesirable effect of reducing the strength of the tissue. Additionally, temperatures above 85? C. burn the cells and result in the production of too much type 3 collagen which is scar tissue, and which has little elasticity. The method of the present invention can therefore produce superior results in the tissue targeted as compared to prior results that induced higher target tissue temperatures.

[0064] Additionally, prior devices that have been used for various applications employ relatively low power levels of approximately 20 watts. Such low power levels were necessary because electrical current tended to flow out from one localized portion of a much larger metal electrode that was in direct contact with the skin, thus producing heating over a very small area that approached a point heat source. A power of greater than 20 watts presented a threat of burning tissue.

[0065] In contrast, the device of the present invention assures that energy will be applied generally uniformly over a relatively large area, namely, over the entire area of the electrode 20. The device is capable of delivering a total power of about 200 watts without risking tissue burning. Even though the target tissue will be brought to a relatively modest temperature of about 40-45? C., the high wattage of the present device provides the advantage of providing more uniform energy distribution over a known area of application and using a shorter pulse of RF energy. Because the present invention allows a higher power level, distributing that power over a broader area, the present invention allows full treatment over a given area in less total treatment time that some of the previous devices required.

[0066] 3. Treating Fecal Incontinence

[0067] The device 10 including the electrode 20 can also be used for treating fecal incontinence in both male and female patients. For treating fecal incontinence, the same biological thermal responses discussed above apply to this treatment. The target tissue includes: the perineum 140 including perineum epithelium, tissue surrounding the rectum, the internal rectal sphincter, and the external rectal sphincter.

[0068] For treating areas in and around the anus 130, it is important to avoid the prostate area in men and the rectal mucosa above the dentate line.

[0069] 4. Vaginal Treatment

[0070] The method and device of the present invention could also be used to treat vaginal epithelium within the vagina 102, including vaginal epithelium within the region from about 3.5 cm past the introitus which the area at the vaginal opening to the end of the vagina which is generally about 8-12 cm past the introitus, to achieve vaginoplasty.

[0071] The method and device can also be used to treat pelvic pain, including dyspareunia which his painful intercourse.

[0072] Chronic pelvic pain is multifactorial and may be caused by several inflammatory processes including chronic infectious cystitis, interstitial cystitis endometriosis and pelvic inflammatory disease. Neurological trauma or diseases in the pelvic floor affecting the innervation of the pudendal, ilioinguinal, iliohypogastric and genitofemoral nerves may also cause pelvic pain conditions from neuropathy and muscle spasms. Pelvic neuralgias are described as causing pelvic pain conditions and associated bladder, bowel, and sexual dysfunctions through direct damage and production of inflammatory processes. The inflammatory mediators may including cytokines, chemokines, free radicals, prostaglandins, cyclooxygenase and matrix metalloproteinase growth and transcription factors, microRNAs, creating a unfriendly microenvironment. Treatment of pelvic pain with physical therapy, nerve blocks has been well described in the literature. Clinical effectiveness with pulsed high-frequency radiofrequency (PRF) treatment applied to the pudendal nerve under ultrasound guidance has been described by Ozkan D, et al., Anaesthesist; 2016 February; 65(2):134-6. doi: 10.1007/s00101-015-0133-4; Epub 2016 Jan. 26. Radiofrequency.

[0073] A treatment method using the device 10 may improve blood flow, reduce muscle spasm and reduce chronic inflammatory diseases by reducing or modulating inflammatory signaling pathways.

[0074] The method and device disclosed here may also increase vaginal lubrication. Heating an area temporarily creates improved blood flow temporarily, which promotes angiogenesis which is the growth of new blood vessels. The new blood vessels lead to improved vaginal lubrication. The histology changes on biopsy immediately induce fibroblast stimulation without disruption of the tissue architecture or cell death. The histology 90 days after treatment produces remodeling of tissue with increased type 1 collagen (i.e., cross-linking, increased fiber size) and reducing the quality of older collagen.

[0075] 5. Treating Pelvic Prolapse

[0076] The method and device of the present invention could also be used to treat pelvis prolapse. The histology changes in collagen from 3 ovines after radiofrequency treatment to the vaginal introitus is described by Vos et al. The histology changes on biopsy immediately induce fibroblast stimulation without disruption of the tissue architecture or cell death. The histology 90 days after treatment produces remodeling of tissue with increased type 1 collagen (i.e., cross-linking, increased fiber size) and reducing the quality of older collagen. These changes of improved quality and strength of collagen along with the shrinkage of collagen bonds described by Wall (mentioned above) may produce the improvement seen in pelvic prolapse.

[0077] After treatment using the method and device of the present invention, patients were examined in the dorsal lithotomy position using the POPQ Staging Criteria measurement system. The patients were again examined at 90 days post treatment. The preliminary data in the initial 22 patients from NTC03280446 Clinicaltrials.gov result reveals a statically significant improvement in the clinical diagnosis of pelvic prolapse.

[0078] 6. Treating Vaginal Laxity

[0079] The method and device of the present invention could also be used to treat vaginal laxity (e.g., patients self-reported vaginal laxity). FIG. 8 illustrates preliminary data for 14 patients from a clinical trial (NTC03280446 Clinicaltrials.gov) using techniques as described herein. The scores prior to treatment (PRE TX) and after treatment (POST TX) reveal a statically significant improvement on the Vaginal Laxity Questionaire (VLQ).

[0080] 7. Treating Sexual Dysfunction

[0081] The method and device of the present invention could also be used to treat sexual dysfunction. FIG. 9 illustrates preliminary data for 14 patients from a clinical trial (NTC03280446 Clinicaltrials.gov) using techniques as described herein. The scores prior to treatment (PRE TX) and after treatment (POST TX) reveal a statically significant improvement on the Female Sexual Function Inventory (FSFI) in 7 of the 14 patients who were diagnosed with sexual dysfunction (FSFI<26.5).

[0082] 8. Treating Female Sexual Desire

[0083] The method and device of the present invention could also be used to treat sexual desire. FIG. 10 illustrates preliminary data for 14 patients from a clinical trial (NTC03280446 Clinicaltrials.gov) using techniques as described herein. The scores prior to treatment (PRE TX) and after treatment (POST TX) reveal a statically significant improvement on the Desire Domain of the Female Sexual Function Inventory (FSFI: Desire).

[0084] 9. Treating Female Sexual Arousal

[0085] The method and device of the present invention could also be used to treat sexual arousal. FIG. 11 illustrates preliminary data for 14 patients from a clinical trial (NTC03280446 Clinicaltrials.gov) using techniques as described herein. The scores prior to treatment (PRE TX) and after treatment (POST TX) reveal a statically significant improvement on the Arousal Domain of the Female Sexual Function Inventory (FSFI: Arousal).

[0086] 10. Treating Female Sexual Satisfaction

[0087] The method and device of the present invention could also be used to treat sexual satisfaction. FIGS. 12 and 13 illustrates preliminary data for 14 patients from a clinical trial (NTC03280446 Clinicaltrials.gov) using techniques as described herein. The scores prior to treatment (PRE TX) and after treatment (POST TX) reveal a statically significant improvement on the Sexual Satisfaction Domain of the FSFI as well as the Sexual Satisfaction Questionnaire (SSQ).

[0088] 11. Treating Painful Intercourse

[0089] The method and device of the present invention could also be used to treat painful intercourse (dyspareunia). Preliminary data for 22 patients from a clinical trial (NTC03280446 Clinicaltrials.gov) using techniques as described herein. The scores prior to treatment (PRE TX) and after treatment (POST TX) reveal a statically significant improvement on the Pain Domain of the FSFI.

[0090] All features disclosed in the specification, including the claims, abstract, and drawings, and all the steps in any method or process disclosed, may be combined in any combination, except combinations where at least some of such features and/or steps are mutually exclusive. Each feature disclosed in the specification, including the claims, abstract, and drawings, can be replaced by alternative features serving the same, equivalent, or similar purpose, unless expressly stated otherwise. Thus, unless expressly stated otherwise, each feature disclosed is one example only of a generic series of equivalent or similar features.

[0091] It will be appreciated that the term present invention as used herein should not be construed to mean that only a single invention having a single essential element or group of elements is presented. Similarly, it will also be appreciated that the term present invention encompasses a number of separate innovations which can each be considered separate inventions. Although the present invention has thus been described in detail with regard to the preferred embodiments and drawings thereof, it should be apparent to those skilled in the art that various adaptations and modifications of the present invention may be accomplished without departing from the spirit and the scope of the invention. Accordingly, it is to be understood that the detailed description and the accompanying drawings as set forth hereinabove are not intended to limit the breadth of the present invention, which should be inferred only from the following claims and their appropriately construed legal equivalents.