PATENT ABSTRACT
Devices, systems and methods for compressing, cutting, incising, reconfiguring, remodeling, attaching, repositioning, supporting, dislocating or altering the composition of tissues or anatomical structures to alter their positional or force relationship to other tissues or anatomical structures. In some applications, the invention may be used to used to improve patency or fluid flow through a body lumen or cavity (e.g., to limit constriction of the urethra by an enlarged prostate gland).

PATENT DESCRIPTION
This application is a divisional of U.S. application Ser. No. 11/134,870, filed May 20, 2005, which is expressly incorporated herein by reference. 
    
    
     FIELD OF THE INVENTION 
     The present invention relates generally to medical devices and methods and more particularly to devices, systems and methods for treating conditions wherein a tissue (e.g., the prostate gland) has a) become enlarged and/or b) undergone a change in form, position, structure, rigidity or force exertion with respect to another anatomical structure and/or c) has begun to impinge upon or compress an adjacent anatomical structure (e.g., the urethra). 
     BACKGROUND OF THE INVENTION 
     There are numerous pathological and nonpathological conditions in which a tissue (e.g., a gland, tumor, cyst, muscle, fascia, skin, adipose, mucous membrane, etc.) becomes enlarged, changed form or position and/or causes unwanted impingement, obstruction, occlusion, stretching, sagging, caving, expulsion and/or collapse of an adjacent body lumen or anatomical structure (e.g., the urethra). Examples of specific conditions which illustrate these medical problems include tissue relaxation or collapse (loose skin, fat or muscle folds, vaginal, rectal, or bladder prolapse, incontinence, etc.), tissue remodeling (scar formation, bladder stiffness secondary to chronic overexertion, infiltrative lung disease), traumatic injury, surgical manipulation (i.e. removal of supportive tissues, removal of tumors, reattachment of ligaments, etc.), tissue growth or enlargement (i.e. benign growths, cancers, angiomas, bone spurs, etc.), luminal obstruction or occlusion (coronary artery disease, peripheral vascular disease, stroke, non-communicating hydrocephalus, infertility secondary to non-patent fallopian tubes, urinary tract obstruction, etc.), tissue impingement (slipped spinal disks, degenerative joint disease, etc.), and ptosis. 
     In particular, Benign Prostatic Hyperplasia (BPH) is one of the most common medical conditions that affect men, especially elderly men. It has been reported that, in the United Sates, more than half of all men have histopathologic evidence of BPH by age 60 and, by age 85, approximately 9 out of 10 men suffer from the condition. Moreover, the incidence and prevalence of BPH are expected to increase as the average age of the population in developed countries increases. 
     The prostate gland enlarges throughout a man&#39;s life. In some men, the prostatic capsule around the prostate gland may prevent the prostate gland from enlarging further. This causes the inner region of the prostate gland to squeeze the urethra. This compression of the urethra increases resistance to urine flow through the region of the urethra enclosed by the prostate. Thus the urinary bladder has to exert more pressure to force urine through the increased resistance of the urethra. Chronic over-exertion causes the muscular walls of the urinary bladder to remodel and become stiffer. This combination of increased urethral resistance to urine flow and stiffness and hypertrophy of urinary bladder walls leads to a variety of lower urinary tract symptoms (LUTS) that may severely reduce the patient&#39;s quality of life. These symptoms include weak or intermittent urine flow while urinating, straining when urinating, hesitation before urine flow starts, feeling that the bladder has not emptied completely even after urination, dribbling at the end of urination or leakage afterward, increased frequency of urination particularly at night, urgent need to urinate etc. 
     In addition to patients with BPH, LUTS may also be present in patients with prostate cancer, prostate infections, and chronic use of certain medications (e.g. ephedrine, pseudoephedrine, phenylpropanolamine, antihistamines such as diphenhydramine, chlorpheniramine etc.) that cause urinary retention especially in men with prostate enlargement. 
     Although BPH is rarely life threatening, it can lead to numerous clinical conditions including urinary retention, renal insufficiency, recurrent urinary tract infection, incontinence, hematuria, and bladder stones. 
     In developed countries, a large percentage of the patient population undergoes treatment for BPH symptoms. It has been estimated that by the age of 80 years, approximately 25% of the male population of the United States will have undergone some form of BPH treatment. At present, the available treatment options for BPH include watchful waiting, medications (phytotherapy and prescription medications), surgery and minimally invasive procedures. 
     For patients who choose the watchful waiting option, no immediate treatment is provided to the patient, but the patient undergoes regular exams to monitor progression of the disease. This is usually done on patients that have minimal symptoms that are not especially bothersome. 
     Medications for treating BPH symptoms include phytotherapy and prescription medications. In phytotherapy, plant products such as Saw Palmetto, African Pygeum, Serenoa repens (sago palm) and South African star grass are administered to the patient. Prescription medications are prescribed as first line therapy in patients with symptoms that are interfering with their daily activities. Two main classes of prescription medications are alpha-1a-adrenergic receptors blockers and 5-alpha-reductase inhibitors. Alpha-1a-adrenergic receptors blockers block that activity of alpha-1a-adrenergic receptors that are responsible for causing constriction of smooth muscle cells in the prostate. Thus, blocking the activity of alpha-1a-adrenergic receptors causes prostatic smooth muscle relaxation. This in turn reduces urethral resistance thereby reducing the severity of the symptoms. 5-alpha-reductase inhibitors block the conversion of testosterone to dihydrotestosterone. Dihydrotestosterone causes growth of epithelial cells in the prostate gland. Thus 5-alpha-reductase inhibitors cause regression of epithelial cells in the prostate gland and hence reduce the volume of the prostate gland which in turn reduces the severity of the symptoms. 
     Surgical procedures for treating BPH symptoms include Transurethal Resection of Prostate (TURP), Transurethral Electrovaporization of Prostate (TVP), Transurethral Incision of the Prostate (TUIP), Laser Prostatectomy and Open Prostatectomy. 
     Transurethal Resection of Prostate (TURP) is the most commonly practiced surgical procedure implemented for the treatment of BPH. In this procedure, prostatic urethral obstruction is reduced by removing most of the prostatic urethra and a sizeable volume of the surrounding prostate gland. This is carried out under general or spinal anesthesia. In this procedure, a urologist visualizes the urethra by inserting a resectoscope, that houses an optical lens in communication with a video camera, into the urethra such that the distal region of the resectoscope is in the region of the urethra surrounded by the prostate gland. The distal region of the resectoscope consists of an electric cutting loop that can cut prostatic tissue when an electric current is applied to the device. An electric return pad is placed on the patient to close the cutting circuit. The electric cutting loop is used to scrape away tissue from the inside of the prostate gland. The tissue that is scraped away is flushed out of the urinary system using an irrigation fluid. Using a coagulation energy setting, the loop is also used to cauterize transected vessels during the operation. 
     Another example of a surgical procedure for treating BPH symptoms is Transurethral Electrovaporization of the Prostate (TVP). In this procedure, a part of prostatic tissue squeezing the urethra is desiccated or vaporized. This is carried out under general or spinal anesthesia. In this procedure, a resectoscope is inserted transurethrally such that the distal region of the resectoscope is in the region of the urethra surrounded by the prostate gland. The distal region of the resectoscope consists of a rollerball or a grooved roller electrode. A controlled amount of electric current is passed through the electrode. The surrounding tissue is rapidly heated up and vaporized to create a vaporized space. Thus the region of urethra that is blocked by the surrounding prostate gland is opened up. 
     Another example of a surgical procedure for treating BPH symptoms is Transurethral Incision of the Prostate (TUIP). In this procedure, the resistance to urine flow is reduced by making one or more incisions in the prostrate gland in the region where the urethra meets the urinary bladder. This procedure is performed under general or spinal anesthesia. In this procedure, one or more incisions are made in the muscle of the bladder neck, which is the region where the urethra meets the urinary bladder. The incisions are in most cases are deep enough to cut the surrounding prostate gland tissue including the prostatic capsule. This releases any compression on the bladder neck and causes the bladder neck to spring apart. The incisions can be made using a resectoscope, laser beam etc. 
     Another example of a surgical procedure for treating BPH symptoms is Laser Prostatectomy. Two common techniques used for Laser Prostatectomy are Visual Laser Ablation of the Prostate (VLAP) and the Holmium Laser Resection/Enucleation of the Prostate (HoLEP). In VLAP, a neodymium:yttrium-aluminum-garnet (Nd:YAG) laser is used to ablate tissue by causing coagulation necrosis. The procedure is performed under visual guidance. In HoLEP, a holmium: Yttrium-aluminum-garnet laser is used for direct contact ablation of tissue. Both these techniques are used to remove tissue obstructing the urethral passage to reduce the severity of BPH symptoms. 
     Another example of a surgical procedure for treating BPH symptoms is Photoselective Vaporization of the Prostate (PVP). In this procedure, laser energy is used to vaporize prostatic tissue to relieve obstruction to urine flow in the urethra. The type of laser used is the Potassium-Titanyl-Phosphate (KTP) laser. The wavelength of this laser is highly absorbed by oxyhemoglobin. This laser vaporizes cellular water and hence is used to remove tissue that is obstructing the urethra. 
     Another example of a surgical procedure for treating BPH symptoms is Open Prostatectomy. In this procedure, the prostate gland is surgically removed by an open surgery. This is done under general anesthesia. The prostate gland is removed through an incision in the lower abdomen or the perineum. The procedure is used mostly in patients that have a large (greater than approximately 100 grams) prostate gland. 
     Minimally invasive procedures for treating BPH symptoms include Transurethral Microwave Thermotherapy (TUMT), Transurethral Needle Ablation (TUNA), Interstitial Laser Coagulation (ILC), and Prostatic Stents. 
     In Transurethral Microwave Thermotherapy (TUMT), microwave energy is used to generate heat that destroys hyperplastic prostate tissue. This procedure is performed under local anesthesia. In this procedure, a microwave antenna is inserted in the urethra. A rectal thermosensing unit is inserted into the rectum to measure rectal temperature. Rectal temperature measurements are used to prevent overheating of the anatomical region. The microwave antenna is then used to deliver microwaves to lateral lobes of the prostate gland. The microwaves are absorbed as they pass through prostate tissue. This generates heat which in turn destroys the prostate tissue. The destruction of prostate tissue reduces the degree of squeezing of the urethra by the prostate gland thus reducing the severity of BPH symptoms. 
     Another example of a minimally invasive procedure for treating BPH symptoms is Transurethral Needle Ablation (TUNA). In this procedure, heat induced coagulation necrosis of prostate tissue regions causes the prostate gland to shrink. It is performed using local anesthetic and intravenous or oral sedation. In this procedure, a delivery catheter is inserted into the urethra. The delivery catheter comprises two radiofrequency needles that emerge at an angle of 90 degrees from the delivery catheter. The two radiofrequency needles are aligned are at an angle of 40 degrees to each other so that they penetrate the lateral lobes of the prostate. A radiofrequency current is delivered through the radiofrequency needles to heat the tissue of the lateral lobes to 70-100 degree Celsius at a radiofrequency power of approximately 456 KHz for approximately 4 minutes per lesion. This creates coagulation defects in the lateral lobes. The coagulation defects cause shrinkage of prostatic tissue which in turn reduces the degree of squeezing of the urethra by the prostate gland thus reducing the severity of BPH symptoms. 
     Another example of a minimally invasive procedure for treating BPH symptoms is Interstitial Laser Coagulation (ILC). In this procedure, laser induced necrosis of prostate tissue regions causes the prostate gland to shrink. It is performed using regional anesthesia, spinal or epidural anesthesia or local anesthesia (periprostatic block). In this procedure, a cystoscope sheath is inserted into the urethra and the region of the urethra surrounded by the prostate gland is inspected. A laser fiber is inserted into the urethra. The laser fiber has a sharp distal tip to facilitate the penetration of the laser scope into prostatic tissue. The distal tip of the laser fiber has a distal-diffusing region that distributes laser energy  3600  along the terminal 3 mm of the laser fiber. The distal tip is inserted into the middle lobe of the prostate gland and laser energy is delivered through the distal tip for a desired time. This heats the middle lobe and causes laser induced necrosis of the tissue around the distal tip. Thereafter, the distal tip is withdrawn from the middle lobe. The same procedure of inserting the distal tip into a lobe and delivering laser energy is repeated with the lateral lobes. This causes tissue necrosis in several regions of the prostate gland which in turn causes the prostate gland to shrink. Shrinkage of the prostate gland reduces the degree of squeezing of the urethra by the prostate thus reducing the severity of BPH symptoms. 
     Another example of a minimally invasive procedure for treating BPH symptoms is implanting Prostatic Stents. In this procedure, the region of urethra surrounded by the prostate is mechanically supported to reduce the constriction caused by an enlarged prostate. Prostatic stents are flexible devices that are expanded after their insertion in the urethra. They mechanically support the urethra by pushing the obstructing prostatic tissue away from the urethra. This reduces the constriction of the urethra and improves urine flow past the prostate gland thereby reducing the severity of BPH symptoms. 
     Although existing treatments provide some relief to the patient from symptoms of BPH, they have significant disadvantages. Alpha-1a-adrenergic receptors blockers have side effects such as dizziness, postural hypotension, lightheadedness, asthenia and nasal stuffiness. Retrograde ejaculation can also occur. 5-alpha-reductase inhibitors have minimal side effects, but only a modest effect on BPH symptoms and the flow rate of urine. In addition, anti-androgens, such as 5-alpha-reductase, require months of therapy before LUTS improvements are observed. Surgical treatments of BPH carry a risk of complications including erectile dysfunction; retrograde ejaculation; urinary incontinence; complications related to anesthesia; damage to the penis or urethra, need for a repeat surgery etc. Even TURP, which is the gold standard in treatment of BPH, carries a high risk of complications. Adverse events associated with this procedure are reported to include retrograde ejaculation (65% of patients), post-operative irritation (15%), erectile dysfunction (10%), need for transfusion (8%), bladder neck constriction (7%), infection (6%), significant hematuria (6%), acute urinary retention (5%), need for secondary procedure (5%), and incontinence (3%) Typical recovery from TURP involves several days of inpatient hospital treatment with an indwelling urethral catheter, followed by several weeks in which obstructive symptoms are relieved but there is pain or discomfort during micturition. 
     The reduction in the symptom score after minimally invasive procedures is not as large as the reduction in symptom score after TURP. Up to 25% of patients who receive these minimally invasive procedures ultimately undergo a TURP within 2 years. The improvement in the symptom score generally does not occur immediately after the procedure. For example, it takes an average of one month for a patient to notice improvement in symptoms after TUMT and 1.5 months to notice improvement after ILC. In fact, symptoms are typically worse for these therapies that heat or cook tissue, because of the swelling and necrosis that occurs in the initial weeks following the procedures. Prostatic stents often offer more immediate relief from obstruction but are now rarely used because of high adverse effect rates. Stents have the risk of migration from the original implant site (up to 12.5% of patients), encrustation (up to 27.5%), incontinence (up to 3%), and recurrent pain and discomfort. In published studies, these adverse effects necessitated 8% to 47% of stents to be explanted. Overgrowth of tissue through the stent and complex stent geometries have made their removal quite difficult and invasive. 
     Thus the most effective current methods of treating BPH carry a high risk of adverse effects. These methods and devices either require general or spinal anesthesia or have potential adverse effects that dictate that the procedures be performed in a surgical operating room, followed by a hospital stay for the patient. The methods of treating BPH that carry a lower risk of adverse effects are also associated with a lower reduction in the symptom score. While several of these procedures can be conducted with local analgesia in an office setting, the patient does not experience immediate relief and in fact often experiences worse symptoms for weeks after the procedure until the body begins to heal. Additionally all device approaches require a urethral catheter placed in the bladder, in some cases for weeks. In some cases catheterization is indicated because the therapy actually causes obstruction during a period of time post operatively, and in other cases it is indicated because of post-operative bleeding and potentially occlusive clot formation. While drug therapies are easy to administer, the results are suboptimal, take significant time to take effect, and often entail undesired side effects. 
     Thus there remains a need for the development of new devices, systems and methods for treating BPH as well as other conditions in which one tissue or anatomical structure impinges upon or compresses another tissue or anatomical structure. 
     SUMMARY OF THE INVENTION 
     The present invention provides devices, systems and methods for compressing, cutting, incising, reconfiguring, remodeling, attaching, repositioning, supporting, dislocating or altering the composition of tissues or anatomical structures to alter their positional or force relationship to other tissues or anatomical structures. In some applications, the invention may be used to improve patency or fluid flow through a body lumen or cavity. Examples of body lumens through which flow may be facilitated using the present invention include the urethra, ureter, trachea, bronchus, bronchiole, other respiratory passageway, stomach, duodenum, small intestine, jejunum, illium, colon, cystic duct, hepatic duct, common bile duct, pancreatic duct, the alimentary canal, an endocrine passageway, a lymphatic, etc. Examples of tissues and anatomical structures that may be compressed, cut, incised, reconfigured, remodeled, attached, repositioned, supported, dislocated or compositionally altered by the present invention include the prostate gland, other glands and organs, neoplasms, benign growths, cancerous growths, tumors, cysts, other masses, congenital deformities, structures that have become enlarged due to hypertrophy, hyperplasia, edema, fluid build up, fluid retention, excess fluid production, impeded fluid outflow, etc. 
     In accordance with the invention there are provided devices, systems and methods for implanting devices within the body to compress tissue in a manner that relieves pressure exerted on or interference with an adjacent anatomical structure. The implantable devices useable for this purpose generally comprising anchoring elements and tensioning elements that extend between the anchoring elements. The anchoring elements are implanted at selected locations and the tensioning elements then draw or pull the anchoring elements toward one another, thereby compressing tissue between the anchoring elements. In applications where these devices are implanted to treat prostatic enlargement, anchoring and tensioning element(s) are implanted and tensioned to compress or reposition prostatic tissue thereby lessening prostate induced constriction of the urethra. In at least some applications, this invention may be used to treat prostatic enlargement without causing substantial damage to the urethra (e.g., forming an opening in the urethra no larger than about 2 mm in its greatest cross-dimension). As used herein, the term “compress” includes not only actual compression of the tissue but also any application of pressure or force upon the tissue that causes the intended therapeutic effect by reconfiguring, remodeling, repositioning or altering the tissue. 
     Still further in accordance with the invention there are provided devices, systems and methods for cutting tissue(s) of the body in a manner that relieves pressure exerted on or interference with an adjacent anatomical structure. In some applications of the invention, one or more working devices may be inserted into the body and used to incise the capsule of an encapsulated organ, tumor, mass or other structure, thereby relieving the capsule&#39;s constraint of the encapsulated organ, tumor, mass or other structure and allowing the encapsulated organ, tumor, mass or other structure to expand, herniate, evulse, splay, spread apart, reconfigure or move in a way that results in decreased pressure on, or decreased interference with, the adjacent anatomical structure. In applications where the invention is used to treat prostatic enlargement, a cutting device may be anchoring and tensioning element(s) are implanted and tensioned to compress or reposition prostatic tissue thereby lessening prostate induced constriction of the urethra. 
     Additional and more specific aspects, elements, steps, applications, embodiments and examples of the invention will be understood by those of skill in the art upon reading of the detailed description and claims set forth herebelow. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         FIG. 1A  is a sagittal sectional view of a male human body through the lower abdomen showing the male urinary tract. 
         FIG. 1B  is a coronal sectional view through the lower abdomen of a human male showing a region of the male urogenital system. 
         FIG. 2A  is a coronal sectional view through the prostate gland and adjacent structures showing a first trans-urethral approach that may be used to implant tissue compression devices(s) (e.g., clips, compression elements, anchoring elements, etc.) to compress or modify the shape of the prostate gland. 
         FIG. 2B  is a coronal sectional view through the prostate gland and adjacent structures showing a second trans-urethral approach that may be used to implant tissue compression devices(s) (e.g., clips, compression elements, anchoring elements, etc.) to compress or modify the shape of the prostate gland. 
         FIG. 2C  is a coronal sectional view through the prostate gland and adjacent structures showing a third trans-urethral approach that may be used to implant tissue compression devices(s) (e.g., clips, compression elements, anchoring elements, etc.) to compress or modify the shape of the prostate gland. 
         FIG. 2D  is a coronal sectional view through the prostate gland and adjacent structures showing a transperineal approach that may be used to implant tissue compression devices(s) (e.g., clips, compression elements, anchoring elements, etc.) to compress or modify the shape of the prostate gland. 
         FIG. 2E  is a coronal sectional view through the prostate gland and adjacent structures showing a percutaneous approach that may be used to implant tissue compression devices(s) (e.g., clips, compression elements, anchoring elements, etc.) to compress or modify the shape of the prostate gland. 
         FIG. 2F  is a coronal sectional view through the prostate gland and adjacent structures showing a percutaneous trans-osseus approach that may be used to implant tissue compression devices(s) (e.g., clips, compression elements, anchoring elements, etc.) to compress or modify the shape of the prostate gland. 
         FIG. 2G  is a coronal sectional view through the prostate gland and adjacent structures showing a percutaneous suprapubic approach that may be used to implant tissue compression devices(s) (e.g., clips, compression elements, anchoring elements, etc.) to compress or modify the shape of the prostate gland. 
         FIG. 2H  is a sagittal sectional view through the prostate gland and adjacent structures showing a percutaneous infrapubic approach that may be used to implant tissue compression devices(s) (e.g., clips, compression elements, anchoring elements, etc.) to compress or modify the shape of the prostate gland. 
         FIG. 2I  is a sagittal sectional view through the prostate gland and adjacent structures showing a trans-rectal approach that may be used to implant tissue compression devices(s) (e.g., clips, compression elements, anchoring elements, etc.) to compress or modify the shape of the prostate gland. 
         FIGS. 3A to 3H  show various components of a system for treating prostate gland disorders by compressing a region of the prostate gland. 
         FIG. 3A  shows the perspective view of an introducer device. 
         FIG. 3B  shows a perspective view of an injecting needle that may be used for injecting one or more diagnostic or therapeutic agents in the anatomy. 
         FIG. 3C  shows a perspective view of an introducing sheath. 
         FIG. 3D  shows a perspective view of a trocar. 
         FIG. 3E  shows a perspective view of an anchor delivery device. 
         FIG. 3F  shows an enlarged view of the distal region of the device in  FIG. 3E . 
         FIG. 3G  shows a perspective view of deployed anchors showing radially expanded splayable arms of proximal anchor and distal anchor. 
         FIG. 3H  shows a perspective view from the proximal direction of a particular embodiment of the attachment mechanism of  FIG. 3E . 
         FIGS. 4A through 4H  show a coronal section through the prostate gland showing the various steps of a method of treating prostate gland disorders by compressing a region of the prostate gland using the kit shown in  FIGS. 3A through 3H . 
       FIGS.  4 G′ through  4 H′ show the final steps of an embodiment of method of treating prostate gland disorders by deploying a proximal anchor in the urethra. 
       FIG.  4 H″ shows a coronal section through the prostate gland showing a final deployed configuration of an embodiment of bone anchoring devices for treating prostate gland disorders by compressing a region of the prostate gland. 
         FIGS. 4I and 4J  is a crossectional view through the prostatic urethra (i.e., the portion of the urethra that passes through the prostate gland) showing the appearance of the urethral lumen before and after performing the method shown in  FIGS. 4A through 4H . 
         FIGS. 5A through 5I  show perspective views of some designs of the tension elements that can be used in the embodiments disclosed elsewhere in this patent application. 
         FIG. 5A  shows a perspective view of a tension element comprising a single strand of an untwisted material. 
         FIG. 5B  shows a perspective view of a tension element comprising one or more serrations or notches. 
         FIG. 5C  shows a perspective view of a tension element comprising multiple filaments of a material twisted together. 
         FIG. 5D  shows a perspective view of a tension element comprising a flexible, elastic, spiral or spring element. 
         FIG. 5E  shows a perspective view of a tension element comprising a screw threading on the outer surface of tension element. 
         FIG. 5F  shows a perspective view of a tension element comprising a hollow shaft comprising one or more collapsible regions. 
         FIG. 5G  shows a perspective view of an anchoring device  522  comprising a tension element and two anchors. 
         FIG. 5H  shows a perspective view of a tensioning element device comprising a detachable region. 
         FIG. 5I  shows a perspective view of a tensioning element comprising telescoping tubes. 
         FIGS. 6A through 11B  show various examples of anchor designs and/or anchoring device designs. 
         FIGS. 6A and 6B  show perspective views of two states of a crumpling anchor. 
         FIGS. 7A and 7B  show sectional views of an undeployed configuration and a deployed configuration respectively of a deployable anchor. 
         FIGS. 8A and 8B  show sectional views of an undeployed configuration and a deployed configuration respectively of a “T” shaped deployable anchor. 
         FIGS. 9A through 9D  show various alternate configurations of the anchoring arms in  FIGS. 7A and 7B . 
       FIGS.  10 A and  10 A′ show a distal view and a perspective view respectively of an anchor comprising a spiral element having a three dimensional shape. 
       FIGS.  10 B and  10 B′ show a distal view and a side view respectively of an anchor comprising a spiral element having a two dimensional shape. 
       FIGS.  10 C and  10 C′ show a distal view and a perspective view respectively of an anchor comprising one or more circular elements. 
         FIG. 10D  shows a perspective view of an embodiment of an anchoring device comprising an outer ring. 
         FIG. 10E  shows a partial perspective view of an anchoring device comprising a hemostatic element. 
         FIG. 11A  shows a perspective view of a device having a set of anchors comprising a curved sheet. 
         FIGS. 12A through 171  show further examples of anchor designs and/or anchoring device designs.  FIG. 12A  shows a perspective view of an anchor comprising an arrowhead. 
         FIG. 12B  shows a crossectional view of an anchor comprising a cup-shaped element that encloses a cavity. 
         FIG. 12C  shows a perspective view of an anchor comprising a screw. 
         FIGS. 13A and 13B  show perspective views of an uncollapsed state and a collapsed state respectively of an anchor comprising a collapsible region. 
         FIGS. 13C and 13D  show perspective views of an undeployed state and a deployed state respectively of an anchor comprising radially spreading arms. 
         FIG. 13E  shows perspective views of an alternate embodiment of an undeployed state of an anchor comprising radially spreading arms. 
         FIGS. 14A and 14B  show perspective views of anchoring devices comprising an adhesive delivering element. 
         FIGS. 15A and 15B  show two configurations of an anchoring device comprising a ratcheted tension element. 
         FIG. 16  shows a perspective view of an anchor comprising a trocar lumen. 
         FIG. 17A  shows a perspective view in the undeployed state of an anchor comprising a rigid or partially flexible T element and a crumpling element. 
         FIGS. 17B and 17C  show various steps of a method to deploy the anchoring device shown in  FIG. 17A . 
         FIGS. 17D ,  17 E and  17 E′ show perspective views and a cross-sectional view of an anchor comprising a rigid or partially flexible T element with one or more openings or perforations. 
         FIGS. 17F and 17G  show perspective views of an undeployed and deployed configuration of an anchor comprising a stent. 
         FIGS. 17H and 17I  show perspective views of an undeployed and deployed configuration of an anchor comprising a spring. 
         FIGS. 18A through 22E  show various embodiments of mechanisms to deploy one or more anchors.  FIGS. 18A and 18B  show a crossection of an anchor deploying mechanism comprising a screw system. 
         FIGS. 19A and 19B  show a crossectional view of an anchor deploying system comprising an electrolytic detachment element. 
         FIG. 20  shows a perspective view of an anchor deploying system comprising a looped ribbon. 
         FIG. 21A  shows a crossectional view of an anchor deploying system comprising a locked ball. 
         FIGS. 21B and 21C  show a method of deploying an anchor comprising a locked ball. 
         FIGS. 22A through 22C  show various views of an anchor deploying system comprising two interlocking cylinders. 
         FIGS. 22D and 22E  show the steps of a method of unlocking the two interlocking cylinders from the anchor deploying systems of  FIGS. 22A through 22C . 
         FIG. 23A  shows a perspective view of a distal end of an anchoring device that has an imaging modality. 
         FIGS. 23B through 23G  show various steps of a method for compressing an anatomical region using the anchoring device of  FIG. 23A . 
       FIGS.  24 A through  24 C′ show the device and various steps of a method of compressing an anatomical region using a device with deploying arms deployed through a trocar. 
         FIG. 24D  shows a crossection through the deployed anchoring device of  FIG. 24A . 
         FIG. 25A  shows a perspective view of a spring clip that can be used to spread the anatomy. 
         FIGS. 25B through 25F  show various steps of a method of spreading an anatomical region or regions using the spring clip of  FIG. 25A . 
         FIGS. 26A and 26B  show a crossectional view and a perspective view respectively of a mechanism of cinching a tension element or tether to an anchor. 
         FIGS. 26C and 26D  show a partial section through a cinching mechanism comprising a cam element. 
         FIG. 26E  shows a sectional view of an embodiment of a cinching mechanism comprising a locking ball. 
         FIG. 26F  shows a side view of an embodiment of a cinching mechanism comprising multiple locking flanges. 
         FIG. 26G  shows an end view of body of  FIG. 26F . 
         FIG. 26H  shows a side view of an embodiment of a cinching mechanism comprising a single locking flange. 
         FIG. 26I  shows an end view of body of  FIG. 26H . 
         FIG. 26J  shows an end view of a cinching mechanism comprising a crimping lumen. 
         FIGS. 26K and 26L  show crossections of an embodiment of a cinching mechanism comprising a crimping anchor in the undeployed and deployed configurations respectively. 
         FIG. 26M  shows a perspective view of an embodiment of a cinching mechanism comprising an element providing a tortuous path to a tension element. 
         FIG. 26N  shows a crossectional view of an embodiment of a locking mechanism comprising a space occupying anchor securely attached to a tension element. 
         FIGS. 26O and 26P  shows a partial sectional view and a perspective view of an embodiment of a cinching mechanism comprising a punched disk. 
         FIGS. 26Q and 26R  show a perspective view of a first embodiment of a cutting device before and after cutting an elongate element. 
         FIG. 26S  show a crossectional view of a second embodiment of a cutting device for cutting an elongate element. 
         FIGS. 27A through 27D  show axial sections through the prostate gland showing various configurations of anchoring devices comprising distal anchors and a tension element. 
         FIGS. 28 and 28A  show perspective views of an embodiment of an anchoring device comprising an elongate element comprising multiple barbs or anchors. 
         FIGS. 28B through 28E  show a coronal section through the prostate gland showing various steps of a method of treating the prostate gland using the device of  FIG. 28 . 
         FIG. 29A  shows an axial section of the prostate gland showing a pair of implanted magnetic anchors. 
         FIGS. 29B through 29D  show a coronal section through the prostate gland showing the steps of a method of implanting magnetic anchors of  FIG. 29A . 
         FIG. 30A  is a coronal sectional view of a portion of the male urogenital system showing a transurethral approach that may be used to perform a prostate cutting procedure of the present invention. 
         FIG. 30B  is a coronal sectional view of a portion of the male urogenital system showing another transurethral approach that may be used to perform a prostate cutting procedure of the present invention. 
         FIG. 30C  is a coronal sectional view of a portion of the male urogenital system showing a transurethral/transvesicular approach that may be used to perform a prostate cutting procedure of the present invention. 
         FIG. 30D  is a coronal sectional view of a portion of the male urogenital system showing another transurethral approach that may be used to perform a prostate cutting procedure of the present invention, wherein a device advances from the urethra, through the prostate gland, and thereafter accesses the prostate capsule from its outer surface. 
         FIG. 31  is a coronal sectional view of a portion of the male urogenital system showing a percutaneous/infrapubic approach that may be used to perform a prostate cutting procedure of the present invention. 
         FIG. 32  is a coronal sectional view of a portion of the male urogenital system showing a percutaneous/transvesicular approach that may be used to perform a prostate cutting procedure of the present invention. 
         FIGS. 33A-33E  shows perspective views of various devices that may be included in a system for performing a prostate cutting procedure in accordance with the present invention. 
         FIG. 33A  shows a perspective view of an introducer device comprising a first tubular element having a working device lumen. 
         FIG. 33B  shows a perspective view of an injecting needle that may be used for injecting one or more diagnostic or therapeutic substances. 
         FIG. 33C  shows a perspective view of a guiding device comprising an elongate body comprising a sharp distal tip. 
       FIGS.  33 D-D′ show a perspective view of a RF cutting device. 
         FIG. 33E  shows a perspective view of an embodiment of a plugging device to plug an opening created during a procedure. 
         FIGS. 33F through 33N  show various alternate embodiments of the electrosurgical cutting device in  FIG. 33D . 
         FIGS. 33F and 33G  show perspective views of the distal region of a first alternate embodiment of an electrosurgical cutting device in the undeployed and deployed states respectively. 
         FIGS. 33H and 33I  show perspective views of the distal region of a second alternate embodiment of an electrosurgical cutting device in the undeployed and deployed states respectively. 
         FIGS. 33J through 33L  show perspective views of the distal region of a second alternate embodiment of an electrosurgical cutting device showing the steps of deploying the electrosurgical cutting device. 
         FIGS. 33M through 33N  show perspective views of the distal region of a third alternate embodiment of an electrosurgical cutting device showing the steps of deploying the electrosurgical cutting device. 
         FIG. 34  shows a perspective view of the distal region of a balloon catheter comprising a balloon with cutting blades. 
         FIG. 35  shows a perspective view of the distal region of a balloon catheter comprising a balloon with cutting wires. 
         FIGS. 36A and 36B  series show perspective views of an undeployed state and a deployed state respectively of a tissue displacement device. 
         FIGS. 36C and 36D  show a coronal view and a lateral view respectively of a pair of deployed tissue displacement devices of  FIGS. 36A and 36B  implanted in the prostate gland. 
         FIGS. 36E through 36H  show an axial section through a prostate gland showing the various steps of a method of cutting or puncturing the prostate gland and lining or plugging the cut or puncture. 
         FIGS. 37A through 37K  show an embodiment of a method of treating prostate gland disorders by cutting a region of the prostate gland using the devices described in  FIG. 33A through 33E . 
         FIGS. 38A to 38D  show various components of a kit for treating prostate gland disorders by compressing a region of the prostate gland. 
         FIG. 38A  shows the perspective view of an introducer device. 
         FIG. 38B  shows a perspective view of a bridge device 
         FIG. 38C  shows a perspective view of a distal anchor deployment device 
         FIG. 38D  shows the proximal anchor delivery tool 
         FIG. 38E  shows a close-up perspective view of proximal anchor  3833  mounted on proximal anchor delivery tool of  FIG. 38D . 
     
    
    
     DETAILED DESCRIPTION 
     The following detailed description and the accompanying drawings are intended to describe some, but not necessarily all, examples or embodiments of the invention only and does not limit the scope of the invention in any way. 
     The following detailed description and the accompanying drawings are intended to describe some, but not necessarily all, examples or embodiments of the invention only and does not limit the scope of the invention in any way. 
     A number of the drawings in this patent application show anatomical structures of the male reproductive and/or urinary system. In general, these anatomical structures are labeled with the following reference letters:
         Urethra UT   Urethral Lumen UL   Urethral Opening UO   Urinary Bladder UB   Ureters UR   Prostate Gland PG   Capsule of Prostate Gland CP   Testis TS   Vas Deferens VD       

       FIG. 1A  shows a sagittal section of a male human body through the lower abdomen showing the male urinary tract. The male urinary tract comprises a pair of tubular organs called ureters (UR) that conduct urine produced by the kidneys. The ureters empty into the urinary bladder. The urinary bladder is a hollow muscular organ that temporarily stores urine. It is situated posterior to the pubic bone. The inferior region of the urinary bladder has a narrow muscular opening called the bladder neck which opens into a soft, flexible, tubular organ called the urethra. The muscles around the bladder neck are called the internal urethral sphincter. The internal urethral sphincter is normally contracted to prevent urine leakage. The urinary bladder gradually fills with urine until full capacity is reached, at which point the sphincter relaxes. This causes the bladder neck to open, thereby releasing the urine stored in the urinary bladder into the urethra. The urethra begins at the bladder neck, terminates at the end of the penis, and allows for urine to exit the body. 
     The region of the urethra just inferior to the urinary bladder is completely surrounded by the prostate gland. The prostate gland is part of the male reproductive system and is usually walnut shaped. Clinically, the prostate is divided into lobes. The lateral lobes are located lateral to the urethra; the middle lobe is located on the dorsal aspect of the urethra, near the bladder neck. Most commonly in BPH, the lateral lobes become enlarged and act like curtains to close the urethral conduit. Less commonly, the middle lobe grows in size and becomes problematic. Because of its superior location near the bladder neck with respect to the urethra, an enlarged middle lobe acts like a ball valve and occludes fluid passage. 
       FIG. 1B  shows a coronal section through the lower abdomen of a human male showing a region of the male urinary system. The prostate gland (PG) is located around the urethra at the union of the urethra and the urinary bladder. 
       FIGS. 2A through 2H  show various alternate approaches to deploy implantable tissue compression device(s) (e.g., one or more clips, anchoring elements, tensioning members, etc.) to compress the prostate gland PG, thereby relieving constriction of the urethra. Specific examples of implantable tissue compression device(s) (e.g., one or more clips, anchoring elements, tensioning members, etc.) useable in this invention are shown in other figures of this patent application and are described more fully herebelow. 
       FIG. 2A  shows a first trans-urethral approach that may be used to implant tissue compression devices(s) to compress the prostate gland PG. In  FIG. 2A , an introducing device  200  is introduced in the urethra through the urethral opening of the penis. Introducing device  200  comprises an elongate body  202  comprising a lumen that terminates distally in a distal opening  204 . One or more working device(s)  206  is/are then introduced through distal opening  204  into the urethra. The working device(s)  206  penetrate the urethral wall and thereafter one or more lobes of the prostate gland. In some applications of the method, working device(s)  206  may further penetrate the prostate capsule and enters the pelvic cavity. Working device(s)  206  are also used to deploy and implant implantable tissue compression device(s) (e.g., one or more clips, anchoring elements, tensioning members, etc.) to compress the prostate gland PG, thereby relieving constriction of the urethra. 
       FIG. 2B  shows a second trans-urethral approach that may be used to implant tissue compression devices(s) to compress the prostate gland PG. In  FIG. 2B , an introducing device  210  is introduced in the urethra through the urethral opening UO of the penis. Introducing device  210  comprises an elongate body  212  comprising a lumen that terminates distally in a distal opening  214 . One or more working device(s)  216  is/are insertable through distal opening  214  into the urethra. Working device(s)  216  penetrate(s) the urethral wall inferior to the prostate gland and enters the pelvic cavity. Thereafter, working device(s)  216  penetrate(s) the prostate capsule CP and thereafter one or more lobes of the prostate gland. In some applications of the method the working device(s)  216  may further penetrate the urethral wall enclosed by the prostate gland EG and enters the urethral lumen. Working device(s)  216  may then be used to deploy and implant implantable tissue compression device(s) (e.g., one or more clips, anchoring elements, tensioning members, etc.) to compress the prostate gland PG, thereby relieving constriction of the urethra. 
       FIG. 2C  shows a third trans-urethral approach that may be used to implant tissue compression devices(s) to compress the prostate gland PG. In  FIG. 2C , an introducing device  220  is introduced in the urethra through the urethral opening UO of the penis. Introducing device  220  comprises an elongate body  222  comprising a lumen that terminates distally in a distal opening  224 . Introducing device  220  is positioned such that distal opening  224  is located in the urinary bladder UB. Thereafter, a one or more working device(s)  226  is/are introduced through distal opening  224  into the urinary bladder UB. Working device(s)  226  penetrate(s) the wall of the urinary bladder UB and thereafter penetrate(s) one or more lobes of the prostate gland PG. In some applications of the method, the working device(s)  226  may further penetrate the prostate capsule and enter the pelvic cavity. Working device(s)  226  may then be used to deploy and implant implantable tissue compression device(s) (e.g., one or more clips, anchoring elements, tensioning members, etc.) to compress the prostate gland PG, thereby relieving constriction of the urethra. 
       FIG. 2D  shows a transperineal approach that may be used to implant tissue compression devices(s) to compress the prostate gland PG. In  FIG. 2D , an introducing device  230  is introduced in the pelvic cavity percutaneously through the perineum. Introducing device  230  comprises an elongate body  232  comprising a lumen that terminates distally in a distal opening  234 . Introducing device  230  is positioned such that distal opening  234  is located in the pelvic cavity adjacent to prostate gland. Thereafter, one or more working device(s)  236  is/are introduced through distal opening  234  into the prostate gland PG. Working device(s)  236  penetrate(s) the prostate capsule CP and thereafter penetrate(s) one or more lobes of the prostate gland PG. In some applications of the method, the working device(s)  236  may further penetrate the urethral wall surrounded by the prostate gland PG and enter the urethral lumen. Working device  236  may then be used to deploy and implant implantable tissue compression device(s) (e.g., one or more clips, anchoring elements, tensioning members, etc.) to compress the prostate gland PG, thereby relieving constriction of the urethra. 
       FIG. 2E  shows a percutaneous/transvesicular approach that may be used to implant tissue compression devices(s) to compress the prostate gland PG. In  FIG. 2E , an introducing device  240  is introduced percutaneously through the abdominal wall. Introducing device  240  comprises an elongate body  242  comprising a lumen that terminates distally in a distal opening  244 . After passing through the abdominal wall, introducing device  240  is advanced through the wall of the urinary bladder UB such that distal opening  244  is located in the urinary bladder UB. Thereafter, one or more working device(s)  246  is/are introduced through distal opening  244  into the urinary bladder UB. One or more working device(s)  246  are advanced through the wall of the urinary bladder UB and into the prostate gland PG. In some applications of the method, working device(s)  246  may further penetrate through the prostate gland capsule and enter the pelvic cavity. Working device(s)  246  is/are then used to deploy and implant implantable tissue compression device(s) (e.g., one or more clips, anchoring elements, tensioning members, etc.) to compress the prostate gland PG, thereby relieving constriction of the urethra. 
       FIG. 2F  shows a percutaneous trans-osseus approach that may be used to implant tissue compression devices(s) to compress the prostate gland PG. In  FIG. 2F , an introducing device  250  is introduced percutaneously through the abdominal wall. Introducing device  250  comprises an elongate body  252  comprising a lumen that terminates distally in a distal opening  254 . Introducing device  250  is used to penetrate a pelvic bone (e.g. the pubic bone PB). Thereafter, introducing device  250  is positioned such that distal opening  254  is located adjacent to the prostate gland PG. Thereafter, one or more working device(s)  256  is/are introduced through distal opening  254  into the prostate gland PG. Working device(s)  256  penetrate the prostate capsule and thereafter penetrate one or more lobes of the prostate gland PG. In some applications of the method, working device(s)  256  may further penetrate the urethral wall surrounded by the prostate gland and enter the urethral lumen. Working device(s)  256  is/are then used to deploy and implant implantable tissue compression device(s) (e.g., one or more clips, anchoring elements, tensioning members, etc.) to compress the prostate gland PG, thereby relieving constriction of the urethra. 
       FIG. 2G  shows a percutaneous suprapubic approach that may be used to implant tissue compression devices(s) to compress the prostate gland PG. In  FIG. 2G , an introducing device  260  is introduced in the pelvic cavity percutaneously in a trajectory that passes superior to the pubis bone. Introducing device  260  comprises an elongate body  262  comprising a lumen that terminates distally in a distal opening  264 . Introducing device  260  is then positioned such that distal opening  264  is located in the pelvic cavity adjacent to prostate gland. Thereafter, one or more working device(s)  266  is/are introduced through distal opening  264  into the prostate gland PG. Working device(s)  266  penetrate the prostate capsule CP and thereafter penetrate one or more lobes of the prostate gland PG. In some applications of the method, working device(s)  266  may further penetrate the urethral wall surrounded by the prostate gland and enter the urethral lumen. Working device(s)  266  is/are then used to deploy and implant implantable tissue compression device(s) (e.g., one or more clips, anchoring elements, tensioning members, etc.) to compress the prostate gland PG, thereby relieving constriction of the urethra.  FIG. 2H  shows a percutaneous infrapubic approach that may be used to implant tissue compression devices(s) to compress the prostate gland. In  FIG. 2H , an introducing device  270  is introduced in the pelvic cavity percutaneously in a trajectory that passes inferior to the pubis bone. Introducing device  270  comprises an elongate body  272  comprising a lumen that terminates distally in a distal opening  274 . Introducing device  270  is introduced percutaneously in the pelvic cavity in a trajectory that passes inferior to the pubic bone. Introducing device  270  is then positioned such that distal opening  274  is located in the pelvic cavity adjacent to prostate gland. Thereafter, one or more working device(s)  276  is/are introduced through distal opening  274  into the prostate gland PG. Working device(s)  276  penetrate the prostate capsule CP and thereafter penetrate one or more lobes of the prostate gland PG. In some applications of the method, working device(s)  276  may further penetrate the urethral wall surrounded by the prostate gland PG and enter the urethral lumen. Working device(s)  276  is/are then used to deploy and implant implantable tissue compression device(s) (e.g., one or more clips, anchoring elements, tensioning members, etc.) to compress the prostate gland PG, thereby relieving constriction of the urethra. 
       FIG. 2I  shows a trans-rectal approach that may be used to implant tissue compression devices(s) to compress the prostate gland PG. In  FIG. 2I , an introducing device  280  is introduced in the rectum. Introducing device  280  comprises an elongate body  282  comprising a lumen that terminates distally in a distal opening  284 . Introducing device is then advanced such that it penetrates the rectal wall and enters the pelvic cavity. Introducing device  280  is then positioned such that distal opening  284  is located in the pelvic cavity adjacent to prostate gland. Thereafter, one or more working device(s)  286  is/are introduced through distal opening  284  into the prostate gland PG. Working device(s)  286  penetrate the prostate capsule CP and thereafter penetrate one or more lobes of the prostate gland. In some applications of the method, working device(s)  286  may further penetrate the urethral wall surrounded by the prostate gland and enter the urethral lumen. Working device(s)  286  is/are then used to deploy and implant implantable tissue compression device(s) (e.g., one or more clips, anchoring elements, tensioning members, etc.) to compress the prostate gland PG, thereby relieving constriction of the urethra. 
       FIGS. 3A to 3F  show various examples of devices and systems that are useable to treat conditions where the prostate gland PG is compressing a region of the urethra such that the urethra does not expand normally during micturition and urine outflow is impeded. 
       FIG. 3A  shows the perspective view of an introducer device  300 . Introducer device  300  comprises an outer body  301  constructed from suitable biocompatible materials including, but not limited to Pebax, Polyimide, Braided Polyimide, Polyurethane, Nylon, PVC, Hytrel, HDPE, PEEK, metals like stainless steel and fluoropolymers like PTFE, PFA, FEP, EPTFE etc. Body  301  comprises a working device lumen  302 . Distal end of working device lumen  302  emerges out of the distal end of body  301 . In one embodiment, distal end of working device lumen  302  has a bent or curved region. Proximal end of working device lumen  302  emerges out of a first flexible tube  304 . The proximal end of first flexible tube  304  comprises a stasis valve  306 . Body  301  further comprises a cystoscope lumen  308 . Distal end of cystoscope lumen  308  emerges out of the distal end of body  301 . Proximal end of cystoscope lumen  308  emerges out of a second flexible tube  310 . The proximal end of second flexible tube  310  comprises a stasis valve  312 . Cystoscope lumen  308  may comprise one or more side ports e.g. a first side port  318  for the introduction or removal of one or more fluids. Working device lumen  302  may comprise one or more side ports e.g. a second side port  320  for the introduction or removal of one or more fluids. 
       FIG. 3B  shows a perspective view of an injecting needle. Injecting needle  330  is used for injecting one or more diagnostic or therapeutic substances. In some applications of the invention, the injecting needle  330  may be used to inject local anesthetic in the urethra, prostate gland and/or tissues near the prostate gland. Specific examples of target areas for injecting local anesthetics are the neurovascular bundles, the genitourinary diaphragm, the region between the rectal wall and prostate, etc. Examples of local anesthetics that can be injected by injecting needle  330  are anesthetic solutions e.g. 1% lidocaine solution; anesthetic gels e.g. lidocaine gels; combination of anesthetic agents e.g. combination of lidocaine and bupivacaine; etc. Injecting needle  330  comprises a hollow shaft  332  made of suitable biocompatible materials including, but not limited to stainless steel 304, stainless steel 306, Nickel-Titanium alloys, titanium etc. In this example, the distal end of hollow shaft  332  comprises a sharp tip  334 . The proximal end of hollow shaft  332  has a needle hub  336  made of suitable biocompatible materials including, but not limited to metals e.g. stainless steel 304, stainless steel 306, Nickel-Titanium alloys, titanium etc.; polymers e.g. polypropylene, Pebax, Polyimide, Braided Polyimide, Polyurethane, Nylon, PVC, Hytrel, HDPE, PEEK, PTFE, PFA, FEP, EPTFE etc. In one embodiment, needle hub  336  comprises a luer lock. 
       FIG. 3C  shows an example of an introducing device or introducing sheath  340 . Introducing sheath  340  comprises a hollow, tubular body  342  made of suitable biocompatible materials including, but not limited to metals e.g. stainless steel 304, stainless steel 306, Nickel-Titanium alloys, titanium etc. or polymers e.g. Pebax, Polyimide, Braided Polyimide, Polyurethane, Nylon, PVC, Hytrel, HDPE, PEEK, PTFE, PFA, FEP, EPTFE etc. Tubular body  342  further comprises two marker bands: a proximal marker band  344  and a distal marker band  346 . The marker bands can be seen by a cystoscope. In one embodiment, proximal marker band  344  and distal marker band  346  are radiopaque. The position of proximal marker band  344  and distal marker band  346  is such that after introducing sheath  340  is placed in an optimum location in the anatomy, proximal marker band  344  is located in the urethra where it can be seen by a cystoscope and distal marker band  346  is located in the prostrate gland or in the wall of the urethra where it cannot be seen by a cystoscope. Tubular body  342  further comprises a series of distance markers  348  on the outer surface of tubular body  342 . The proximal end of tubular body  342  further comprises a hub  350  made of suitable biocompatible materials including, but not limited to metals e.g. stainless steel 304, stainless steel 306, Nickel-Titanium alloys, titanium etc. or polymers e.g. Pebax, Polyimide, Braided Polyimide, Polyurethane, Nylon, PVC, Hytrel, HDPE, PEEK, PTFE, PFA, FEP, EPTFE etc. In one embodiment, hub  350  comprises a luer lock. 
       FIG. 3D  shows a perspective view of a trocar. Trocar  360  comprises a tubular trocar body  362 . The proximal end of trocar body  362  comprises a hub  364 . Trocar body  362  and hub can be constructed from suitable biocompatible materials including, but not limited to metals e.g. stainless steel 304, stainless steel 306, Nickel-Titanium alloys, titanium etc. or polymers e.g. Pebax, Polyimide, Braided Polyimide, Polyurethane, Nylon, PVC, Hytrel, HDPE, PEEK, PTFE, PFA, FEP, EPTFE etc. Distal end of trocar body  362  ends in a sharp trocar tip  366 . 
       FIG. 3E  shows a perspective view of an anchor delivery device. Anchor delivery device  370  comprises a body  372  having a distal opening  373 . A section of the distal region of body  372  has been removed to show a view of the anchor assembly. Body  372  encloses a distal anchor  374  and a proximal anchor  376 . Proximal anchor  376  and distal anchor  374  can have a variety of designs including, but not limited to the designs disclosed elsewhere in this patent application. Proximal anchor  376  and distal anchor  374  can be constructed from suitable biocompatible materials including, but not limited to metals e.g. stainless steel 304, stainless steel 306, Nickel-Titanium alloys, titanium etc. or polymers e.g. Pebax, Polyimide, Braided Polyimide, Polyurethane, Nylon, PVC, Hytrel, HDPE, PEEK, PTFE, PFA, FEP, EPTFE etc. In one embodiment, shown in  FIGS. 3F and 3G , proximal anchor  9976  and distal anchor  9974  comprise splayable elements that expand in a radially outward direction when a radial compression force, as enacted by body lumen  9972 , on proximal anchor  9976  and distal anchor  9974  is removed. The splayable elements can be made of suitable super-elastic materials such as Nickel-Titanium alloys etc. Proximal anchor  9976  and distal anchor  9974  are connected to each other by a tension element  9978 . Tension element  9978  can be made of suitable elastic or non-elastic materials including, but not limited to metals e.g. stainless steel 304, stainless steel 306, Nickel-Titanium alloys, suture materials, titanium etc. or polymers such as silicone, nylon, polyamide, polyglycolic acid, polypropylene, Pebax, PTFE, ePTFE, silk, gut, or any other braided or mono-filament material. Tension element  9978  can have a variety of designs including the designs shown in  FIGS. 5A through 5F . As shown in  FIG. 3E , the proximal end of proximal anchor  9976  is connected by an attachment mechanism  9980  to a torquable shaft  9982 . The proximal end of torquable shaft  9982  is attached to a control button  9984 . Control button  9984  can be used to deploy proximal anchor  9976  by sliding control button  9984  along groove  9985  in the distal direction. Control button  9984  is then used to deploy distal anchor  9974  by turning control button  9984  in the circumferential direction along groove  9985 . 
       FIG. 3H  shows a perspective view from the proximal direction of a particular embodiment of the attachment mechanism of  FIG. 3E . Attachment mechanism  380  comprises a circular plate  386  made from suitable biocompatible materials including, but not limited to metals e.g. stainless steel 304, stainless steel 306, Nickel-Titanium alloys, titanium etc. or polymers e.g. Polycarbonate, PVC, Pebax, Polyimide, Polyurethane, Nylon, Hytrel, HDPE, PEEK, PTFE, PFA, FEP etc. The proximal face of circular plate  386  is connected to torquable shaft  382 . Circular plate  386  further comprises a semicircular groove  388 . One end of semicircular groove  388  comprises an enlarged region  390 . A knob  392  located on the proximal portion of proximal anchor  376  slides on semicircular groove  388 . The size of knob  322  is larger than the size of semicircular groove  388  but smaller than size of enlarged region  390 . This keeps proximal anchor  376  attached to circular plate  386 . When control button  384  is turned in the circumferential direction along groove  385 , torquable shaft  382  is turned. This turns circular plate  386  causing knob  392  to slide on the groove  388 . Ultimately, knob  392  reaches enlarged region  390 . This releases knob  392  from circular plate  386  thereby releasing proximal anchor  376  from anchor delivery device  370 . 
       FIGS. 4A through 4H  show a coronal section through the prostate gland showing the various steps of a method of treating prostate gland disorders by compressing a region of the prostate gland using the kit shown in  FIGS. 3A through 3F . In  FIG. 4A , introducer device  300  is introduced in the urethra through the urethral opening at the tip if the penis. A cystoscope is inserted in introducer device  300  through cystoscope lumen  308  such that the lens of the cystoscope is located in the distal opening of cystoscope lumen. The cystoscope is used to navigate introducer device  300  through the urethra such that the distal region of introducer device  300  is located in a target region in the prostatic urethra. Thereafter in  FIG. 4B , injecting needle  330  is advanced through working device lumen  302  such that the distal tip of injecting needle  330  penetrates into a region of the urethral wall or the prostate gland. Injecting needle  330  is then used to inject one or more diagnostic or therapeutic agents into the urethral wall or the prostate gland. This step may be repeated one or more times to inject one or more diagnostic or therapeutic agents in one or more regions of the urethral wall and/or the prostate gland. In one method embodiment, injecting needle  330  is used to inject an anesthetic in one or more regions of the urethral wall and/or the prostate gland. In another embodiment, injecting needle  330  is used to deliver energy in the form of radiofrequency energy, resistive heating, laser energy, microwave energy etc. In another embodiment, injecting needle  330  is used to deliver alpha antagonist agents, such as phenoxybenzamine, prazosin, doxazosin, terazosin, tamsulosin, alfuzosin etc. In another embodiment, injecting needle  330  is used to deliver anti-androgen, such as flutamide or 5-alpha reductase inhibitors, such as finasteride, dutasteride, 3-oxosteroid compounds, 4-aza-3-oxosteroid derivatives of testosterone etc. In another embodiment, injecting needle  330  is used to deliver anti-inflammatory agents, such as rapamycin, paclitaxel, ABT-578, everolimus, taxol etc. In another embodiment, injecting needle  330  is used to deliver ablative agents such as methyl alcohol etc. 
     In another embodiment, injecting needle  330  is used to deliver energy in the form of radiofrequency energy, resistive heating, laser energy, microwave energy etc. In another embodiment, injecting needle  330  is used to deliver alpha antagonist agents, such as phenoxybenzamine, prazosin, doxazosin, terazosin, tamsulosin, alfuzosin etc. In another embodiment, injecting needle  330  is used to deliver anti-androgen, such as flutamide or 5-alpha reductase inhibitors, such as finasteride, dutasteride, 3-oxosteroid compounds, 4-aza-3-oxosteroid derivatives of testosterone etc. In another embodiment, injecting needle  330  is used to deliver anti-inflammatory agents, such as rapamycin, paclitaxel, ABT-578, everolimus, taxol etc. In another embodiment, injecting needle  330  is used to deliver ablative agents such as methyl alcohol etc. 
     In step  4 C, injecting needle  330  is withdrawn from introducer device  300 . Thereafter, introducer sheath  340  and trocar  360  are advanced through working device lumen  302 . In the example shown, introducer sheath  340  and trocar  360  are advanced till the distal tip of trocar  360  penetrates the capsule of the prostate gland and the distal end of introducer sheath  340  is located outside the prostate gland in the pelvic cavity. Thereafter, trocar  360  is withdrawn from working device lumen  302  leaving introducer sheath  340  in place. In  FIG. 4D , anchor delivery device  370  is introduced through the lumen of introducer sheath  340  till the distal end of body  372  protrudes through the distal tip of introducer sheath  340 . In step  4 E, distal anchor  374  is deployed. It should be noted that the anchor may be carried to the site and deployed from within an introducer, on the outside of an introducer, or it may be the distal tip of the introducer itself. Thereafter, anchor deliver device  370  is pulled in the proximal direction along with introducer sheath  340  so that distal anchor  374  is anchored on the outer surface of the prostate capsule. This step may be used to create tension in the tension element  378 . In one method embodiment, anchor deliver device  370  is pulled in the proximal direction along with introducer sheath  340  such that the distal end of anchor delivery device  370  is located in the prostate gland. In another method embodiment, anchor deliver device  370  is pulled in the proximal direction along with introducer sheath  340  till the distal end of anchor delivery device  370  is located in the urethral wall or the urethral lumen. In step  4 F, proximal anchor  376  is deployed. Proximal anchor  376  may be deployed in the prostate gland, in the urethral wall or in the urethral lumen. Proximal anchor  376  is still attached by attachment mechanism  380  to anchor delivery device  370 . The proximal anchor may be pre-loaded on the tension element, or may subsequently be loaded by the operator on the tension element.  FIGS. 4G through 4H  show the steps of deploying proximal anchor  376  in the prostate gland. In  FIG. 4G , proximal anchor  376  is separated from anchor delivery device  370 . This separation may be achieved via numerous means including cutting, melting, un-locking a link, or breaking the tensioning element at a desired location. Ideally this residual end of the tensioning element will not protrude substantially into the lumen of the urethra. Thus proximal anchor  376  and distal anchor  374  are anchored in the anatomy. Thereafter, anchor delivery device  370  and introducer sheath  340  are both pulled in the proximal direction and are withdrawn into introducer device  300 . Thereafter, introducer device  300  is pulled in the proximal direction to pull it out of the urethra. In  FIG. 4H , the steps from  FIG. 4A through 4G  are repeated in a second region of the prostate gland if desired to implant two or more sets of anchoring devices. 
     Alternatively, FIGS.  4 G′ through  4 H′ show the steps of deploying proximal anchor  376  in the urethra. After the step in  FIG. 4F , in FIG.  4 G′, proximal anchor  376  is separated from anchor delivery device  370  in the urethra. Thus proximal anchor  376  and distal anchor  374  are anchored in the urethra and the prostate capsule respectively. Thereafter, anchor delivery device  370  and introducer sheath  340  are both pulled in the proximal direction and are withdrawn into introducer device  300 . Thereafter, introducer device  300  is pulled in the proximal direction to pull it out of the urethra. In FIG.  4 H′, the steps from FIG.  4 A through  4 G′ are repeated optionally in a second region of the prostate gland to implant two or more sets of anchoring devices. It should be understood that this method and devices may be applied to any lobe (middle or lateral lobes) of the prostate and further more may be used multiple times in the same lobe to achieve the desired effect. 
     FIG.  4 H″ shows a coronal section through the prostate gland showing the final deployed configuration of an embodiment of bone anchoring devices for treating prostate gland disorders by compressing a region of the prostate gland. In the method of deploying this device, introducer sheath  340  and trocar  360  are advanced till the distal tip of trocar  360  penetrates a bone in the abdomen (e.g. the pelvic bone, etc.) and the distal end of introducer sheath  340  is located outside the bone. Thereafter, trocar  360  is withdrawn from working device lumen  302  leaving introducer sheath  340  in place. Thereafter, anchor delivery device  370  is introduced through the lumen of introducer sheath  340  until the distal end of body  372  touches the bone through the distal tip of introducer sheath  340 . Thereafter, distal anchor  374  is implanted in the bone. Distal anchor  374  may comprise a variety of designs including, but not limited to designs of distal tips of Kirschner wires. Examples of such Kirschner wire distal tips are spiral drill tips, lancer tips, threaded trocar tips, lengthwise knurled tips, 3-sided trocar tips, 4-sided trocar tips, Thereafter, anchor deliver device  370  is pulled in the proximal direction along with introducer sheath  340 . This step creates tension in the tension element  378 . In another method embodiment, anchor deliver device  370  is pulled in the proximal direction along with introducer sheath  340  till the distal end of anchor delivery device  370  is located in the urethral wall or the urethral lumen. The remaining method steps are similar to steps  4 F through  4 H. 
     One or more anchors disclosed in this patent application may be implanted in anatomical locations that include, but are not limited to:
         a location within prostatic lobe;   a location within peripheral zone of prostate;   a location within prostatic capsule;   a location between prostatic capsule and pubic fascia;   a location within the pubic fascia;   a location within the levator ani muscle a location within the obturator internus muscle;   a location within the pelvic bone;   a location within the periostium of pelvic bone;   a location within the pubic bone;   a location within the periostium of pubic bone;   a location within the symphysis pubica;   a location within the urinary bladder wall;   a location within the ischiorectal fossa;   a location within the urogenital diaphragm; and   a location within the abdominal fascia.       

       FIGS. 4I and 4J  show a crossection of the urethra through the prostate gland PG showing the appearance of the urethral lumen before and after performing the method shown in  FIGS. 4A through 4H .  FIG. 4I  shows a crossection of the urethra through the prostate gland showing the appearance of the urethral lumen in a patient with BPH.  FIG. 4J  shows a crossection of the urethra through the prostate gland PG showing the appearance of the urethral lumen after performing the procedure shown in  FIGS. 4A through 4H . The urethral lumen shown in  FIG. 4I  is larger than the urethral lumen in  FIG. 4J . 
       FIGS. 5A through 5F  show perspective views of some designs of the tension elements that can be used in the embodiments disclosed elsewhere in this patent application.  FIG. 5A  shows a perspective view of a tension element  500  comprising a single strand of an untwisted material. Examples of materials that can be used to manufacture tension element  500  include but are not limited to synthetic fibers e.g. various grades of Nylon, polyethylene, polypropylene, polyester, Aramid etc.; metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; natural fibers e.g. cotton, silk etc.; rubber materials e.g. various grades of silicone rubber etc.  FIG. 5B  shows a perspective view of a tension element  502  comprising one or more serrations  504  or notches. Serrations  504  may be aligned in a particular direction to allow relatively easy movement of an outer body along tension element  502  in one direction and offer significant resistance to movement of the outer body along the tension element in the other direction.  FIG. 5C  shows a perspective view of a tension element  506  comprising multiple filaments  507  of a material twisted together. Examples of materials that can be used include to manufacture multiple filaments  507  include but are not limited to synthetic fibers e.g. various grades of Nylon, polyethylene, polypropylene, polyester, Aramid etc.; metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; natural fibers e.g. cotton, silk etc.; rubber materials e.g. various grades of silicone rubber etc. multiple filaments  507  may be coated with a coating  508  including, but not limited to a lubricious coating, antibiotic coating, etc. It is also possible for the tension element to comprise a composite braided structure in a plastic/metal or plastic/plastic configuration to reduce profile and increase strength. Such materials could have preset levels of elasticity and non-elasticity.  FIG. 5D  shows a perspective view of a tension element  509  comprising a flexible, elastic, spiral or spring element. Other of the contemplated devices lack a spring (See for example  FIG. 5G , described further below). Examples of materials that can be used include to manufacture tension element  509  include but are not limited to metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.  FIG. 5E  shows a perspective view of a tension element  510  comprising a screw threading  511  on the outer surface of tension element  510 . Screw threading  511  enables tension element  510  to be screwed through an outer element to advance or withdraw tension element through the outer element.  FIG. 5F  shows a perspective view of a tension element  512  comprising a hollow shaft  514  comprising one or more collapsible regions  516 . A collapsible region  516  comprises one or more windows  518 . Windows  518  are cut in hollow shaft  514  in such a way that several thin, collapsible struts  520  are created between adjacent windows  518 . When tension element  512  is compresses along its length, collapsible struts  520  are deformed in the radially outward direction to create one or more anchoring regions. 
       FIG. 5G  shows a perspective view of an anchoring device  522  comprising a tension element and two anchors. Distal end of a tension element  524  is attached to a distal anchor  526 . Proximal end of tension element  524  is attached to a proximal anchor  528 . 
       FIG. 5H  shows a perspective view of a tensioning element device comprising a detachable region. Anchoring device  530  comprises a first anchor  532  and a second anchor  534 . First anchor  532  and second anchor  534  may comprise a variety of anchor designs disclosed elsewhere in this patent application. In one embodiment, one or both of first anchor  532  and second anchor  534  comprise a substantially flat plate. The substantially flat plate may be made from various materials including, but not limited to metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; polymers e.g. polypropylene, Teflon etc.; synthetic fibers e.g. various grades of Nylon, polyethylene, polypropylene, polyester, Aramid etc.; natural fibers e.g. cotton, silk etc.; rubber materials e.g. various grades of silicone rubber etc. First anchor  532  and second anchor  534  are connected to a tensioning element. The tensioning element comprises two flexible members: a first tensioning member  536  and a second tensioning member  538 . The distal end of first tensioning member  536  is connected to first anchor  532  and the proximal end of second tensioning member  538  is connected to second anchor  534 . Proximal end of first tensioning member  536  and distal end of second tensioning member  538  are connected to a releasable member  540 . Releasable member  540  can be releasably connected to a deploying device. In one embodiment of a method using anchoring device  530 , first anchor  532  is deployed out of an anatomical tissue (e.g. the prostate gland) into a first anatomical cavity (e.g. the pelvic cavity). Thereafter, second anchor  534  is deployed into a second anatomical cavity (e.g. the urethral lumen). Thereafter, releasable member  540  is released from the deploying device to deliver anchoring device  530  in a target region. 
       FIG. 5I  shows a perspective view of a tensioning element comprising telescoping tubes. Tensioning element  544  may comprise two or more telescoping tubes. In this example, tensioning element  544  comprises three telescoping tubes: a first telescoping tube  546 , a second telescoping tube  548  and a third telescoping tube  550 . Second telescoping tube  548  slidably fits into a lumen of first telescoping tube  546 . Similarly third telescoping tube  550  slidably fits into a lumen of second telescoping tube  548 . The telescoping tubes have a locking mechanism to prevent a telescoping tube from completely disengaging from another telescoping tube. The telescoping tubes may be made from a variety of biocompatible materials including, but not limited to plastics, metals etc. 
     All the components of the systems disclosed herein (including but not limited to the tensioning elements, inner and outer anchor members) may be coated or embedded with therapeutic or diagnostic substances (e.g., drugs or therapeutic agents) or such therapeutic or diagnostic substances may be introduced into or near the prostate or adjacent tissue through a catheter, cannula needles, etc. Examples of therapeutic and diagnostic substances that may be introduced or eluted include but are not limited to: hemostatic agents; antimicrobial agents (antibacterials, antibiotics, antifungals, antiprotozoals; antivirals; antimicrobial metals (e.g., silver, gold, etc.); hemostatic and/or vasoconstricting agents (e.g., pseudoephedrine, xylometazoline, oxymetazoline, phenylephrine, epinephrine, cocaine, etc.); local anesthetic agents (lidocaine, cocaine, bupivacaine,); hormones; anti-inflammatory agents (steroidal and non-steroidal); hormonally active agents; agents to enhance potency; substances to dissolve, degrade, cut, break, weaken, soften, modify or remodel connective tissue or other tissues; (e.g., enzymes or other agents such as collagenase (CGN), trypsin, trypsin/EDTA, hyaluronidase, and tosyllysylchloromethane (TLCM)); chemotherapeutic or antineoplastic agents; substances that prevent adhesion formation (e.g., hyaluronic acid gel); substances that promote desired tissue ingrowth into an anchoring device or other implanted device; substances that promote or facilitate epithelialization of the urethra or other areas; substances that create a coagulative lesion which is subsequently resorbed causing the tissue to shrink; substances that cause the prostate to decrease in size; phytochemicals that cause the prostate to decrease in size; alpha-1a-adrenergic receptor blocking agents; 5-alpha-reductase inhibitors; smooth muscle relaxants; agents that inhibit the conversion of testosterone to dihydrotestosterone, etc. Specific examples of antitumor agents (e.g., cancer chemotherapeutic agents, biological response modifiers, vascularization inhibitors, hormone receptor blockers, cryotherapeutic agents or other agents that destroy or inhibit neoplasia or tumorigenesis) that may be delivered in accordance with the present invention include but are not limited to; alkylating agents or other agents which directly kill cancer cells by attacking their DNA (e.g., cyclophosphamide, isophosphamide), nitrosoureas or other agents which kill cancer cells by inhibiting changes necessary for cellular DNA repair (e.g., carmustine (BCNU) and lomustine (CCNU)), antimetabolites and other agents that block cancer cell growth by interfering with certain cell functions, usually DNA synthesis (e.g., 6 mercaptopurine and 5-fluorouracil (5FU), antitumor antibiotics and other compounds that act by binding or intercalating DNA and preventing RNA synthesis (e.g., doxorubicin, daunorubicin, epirubicin, idarubicin, mitomycin-C and bleomycin) plant (vinca) alkaloids and other anti-tumor agents derived from plants (e.g., vincristine and vinblastine), steroid hormones, hormone inhibitors, hormone receptor antagonists and other agents which affect the growth of hormone-responsive cancers (e.g., tamoxifen, herceptin, aromatase inhibitors such as aminoglutethimide and formestane, triazole inhibitors such as letrozole and anastrozole, steroidal inhibitors such as exemestane), antiangiogenic proteins, small molecules, gene therapies and/or other agents that inhibit angiogenesis or vascularization of tumors (e.g., meth-1, meth-2, thalidomide), bevacizumab (Avastin), squalamine, endostatin, angiostatin, Angiozyme, AE-941 (Neovastat), CC-5013 (Revimid), medi-522 (Vitaxin), 2-methoxyestradiol (2ME2, Panzem), carboxyamidotriazole (CAI), combretastatin A4 prodrug (CA4P), SU6668, SU11248, BMS-275291, COL-3, EMD 121974, IMC-1C11, IM862, TNP-470, celecoxib (Celebrex), rofecoxib (Vioxx), interferon alpha, interleukin-12 (IL-12) or any of the compounds identified in Science Vol. 289, Pages 1197-1201 (Aug. 17, 2000) which is expressly incorporated herein by reference, biological response modifiers (e.g., interferon, bacillus calmette-guerin (BCG), monoclonal antibodies, interluken 2, granulocyte colony stimulating factor (GCSF), etc.), PGDF receptor antagonists, herceptin, asparaginase, busulphan, carboplatin, cisplatin, carmustine, cchlorambucil, cytarabine, dacarbazine, etoposide, flucarbazone, fluorouracil, gemcitabine, hydroxyurea, ifosphamide, irinotecan, lomustine, melphalan, mercaptopurine, methotrexate, thioguanine, thiotepa, tomudex, topotecan, treosulfan, vinblastine, vincristine, mitoazitrone, oxaliplatin, procarbazine, stereopticon, taxol, taxotere, analogs/congeners and derivatives of such compounds as well as other antitumor agents not listed here. 
     Additionally or alternatively, in some applications such as those where it is desired to grow new cells or to modify existing cells, the substances delivered in this invention may include cells (mucosal cells, fibroblasts, stem cells or genetically engineered cells) as well as genes and gene delivery vehicles like plasmids, adenoviral vectors or naked DNA, mRNA, etc. injected with genes that code for anti-inflammatory substances, etc., and, as mentioned above, macrophages or giant cells that modify or soften tissue when so desired, cells that participate in or effect the growth of tissue. 
       FIGS. 6A through 11A  show various examples of anchor designs and/or anchoring device designs.  FIGS. 6A and 6B  show examples of a crumpling anchor  600 . In  FIG. 6A , crumpling anchor  600  comprises a substantially flattened body  602 . Body  602  can be made of a variety of materials including, but not limited to synthetic fibers e.g. various grades of Nylon, polyethylene, polypropylene, polyester, Aramid etc.; metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; natural fibers e.g. cotton, silk etc.; rubber materials e.g. various grades of silicone rubber etc. Further, in any of the implantable tissue compression devices, any or all of the anchors, the tensioning element(s) and any other components may be coated, impregnated, embedded or otherwise provided with substance(s) (e.g., drugs, biologics, cells, etc.) to reduce the likelihood of infection, inflammation, treat the prostatic adenoma directly or enhance the likelihood of endothelialization, deter adhesion formation, promote healing or otherwise improve the likelihood or degree of success of the procedure. Such substance(s) may be released primarily at the time of delivery or may be released over a sustained period. Examples of such substances are listed above and include but are not limited to certain metals with bacteriostatic action (i.e. silver, gold, etc.), antibiotics, antifungals, hemostatic agents (i.e. collagen, hyaluronic acid, gelfoam, cyano-acrylate, etc.), anti-inflammatory agents (steroidal and non-steroidal), hormonally active agents, stem cells, endothelial cells, genes, vectors containing genes, etc. Body  602  may be non-woven or woven. Body  602  may have a variety of shapes including, but not limited to square, rectangular, triangular, other regular polygonal, irregular polygonal, circular etc. Body  602  may have a substantially one dimensional, two dimensional or three dimensional shape. The material chosen for this device may have hemostatic properties to reduce bleeding from the implantation tract or site. Distal end of body  602  is connected to the distal end of tension element  604 . Body  602  further comprises one or more attachment means  606 . Attachment means are used to create a channel in the body  602  through which tension element  604  passes. Crumpling anchor  600  is introduced through a region of tissue (e.g. through prostate gland tissue) into a cavity or lumen e.g. pelvic cavity, urethral lumen etc. In  FIG. 6B , tension element  604  is pulled in the proximal direction. The causes crumpling (e.g., collapsing) of the crumpling anchor  600  between the tissue and the distal end of tension element  604 . This process prevents tension element  604  in the tissue and prevents further movement of tension element  604  in the proximal direction. 
       FIGS. 7A and 7B  show an example of a deployable anchor  700  in an undeployed configuration and a deployed configuration, respectively. This deployable anchor  700  comprises one or more anchoring arms  702 . Anchoring arms  702  may be made from a variety of elastic, super-elastic or shape memory materials etc. Typical examples of such materials include but are not limited to metals e.g. stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc. Anchoring arms  702  are connected to a central hub  704 . Central hub in turn is connected to the distal end of a tension element  706 . In  FIG. 7A , anchoring arms  702  are folded inside a hollow deploying sheath  708 . This reduces the undeployed diameter of anchoring arms  702  and also prevents unwanted anchoring of anchoring arms  702 . In  FIG. 7B , deploying sheath  708  is pulled in the proximal direction. This releases anchoring arms  702  from the distal end of deploying sheath  702 . This causes anchoring arms  702  to open in the radially outward direction. Anchor  700  can then anchor to tissue and resist movement of tension element  706  in the proximal direction. 
       FIGS. 8A and 8B  show sectional views of an undeployed configuration and a deployed configuration respectively of a “T” shaped deployable anchor. Anchor  8110  comprises an elongate region  802 . Elongate region  802  may be made from a variety of elastic, super-elastic or shape memory materials etc. Typical examples of such materials include but are not limited to metals e.g. stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc; polymers e.g. polypropylene, Teflon etc. Middle section of elongate region  802  is connected to the distal end of a tension element  804  to form a “T” shaped anchor. In one embodiment, middle section of elongate region  802  is connected to the distal end of a tension element  804  by a hinge. In  FIG. 8A , elongate region  802  is folded inside a hollow deploying sheath  806 . This reduces the undeployed diameter of the distal region of anchor  8110  and also prevents unwanted anchoring of elongate region  802  to tissue. In  FIG. 8B , deploying sheath  806  is pulled in the proximal direction. This releases elongate region  802  from the distal end of deploying sheath  806 . This in turn causes elongate region  802  to twist and orient itself perpendicular to the distal end of a tension element  804 . Anchor  800  can then anchor to tissue and resist movement of tension element  804  in the proximal direction. 
     Anchoring arms  702  in  FIGS. 7A and 7B  can have a variety of configurations including, but not limited to configurations shown in  FIGS. 9A through 9D .  FIG. 9A  shows a distal end view of an embodiment of an anchor comprising two triangular arms. Anchor  900  comprises two anchor arms  902 . Anchor arms  902  can be made of a variety of materials including, but not limited to metals e.g. stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc; polymers e.g. polypropylene, Teflon etc. Anchor arms  902  are connected to a tension element  904 . In one embodiment, anchor arms  902  are connected to a central hub, which in turn is connected to tension element  904 . The arms in each of these devices may be folded or contained prior to deployment through the use of a sheath or grasping or mounting device.  FIG. 9B  shows a distal end view of an embodiment of an anchor comprising four rectangular arms. Anchor  906  comprises four anchor arms  908 . Anchor arms  908  can be made of a variety of materials including, but not limited to metals e.g. stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc; polymers e.g. polypropylene, Teflon etc. Anchor arms  908  are connected to a tension element  910 . In one embodiment, anchor arms  908  are connected to a central hub, which in turn is connected to tension element  910 .  FIG. 9C  shows a distal end view of an embodiment of an anchor comprising a mesh or a woven material. Anchor  912  comprises four anchor arms  914 . Anchor arms  914  can be made of a variety of materials including, but not limited to metals e.g. stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc; polymers e.g. polypropylene, Teflon etc. Anchor arms  914  are connected to a tension element  916 . In one embodiment, anchor arms  914  are connected to a central hub, which in turn is connected to tension element  916 . A layer of porous material  918  is located between anchor arms  914 . Porous material  918  comprises a plurality of pores that allow for tissue ingrowth. Porous material  918  may also help to distribute the pressure on anchor arms  914  over a wider area. Porous material  918  can be made of variety of materials including, but not limited to synthetic fibers e.g. various grades of Nylon, polyethylene, polypropylene, polyester, Aramid etc.; metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; natural fibers e.g. cotton, silk etc.; rubber materials e.g. various grades of silicone rubber etc. Porous material  918  may be non-woven or woven. Any of the arms or struts in one or more anchoring devices may comprise bent or curved regions. For example,  FIG. 9D  shows a distal end view of an embodiment of an anchor comprising four curved arms. Anchor  920  comprises four curved anchor arms  922 . Curved anchor arms  922  can be made of a variety of materials including, but not limited to metals e.g. stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc; polymers e.g. polypropylene, Teflon etc. Curved anchor arms  922  are connected to a tension element  924 . In one embodiment, curved anchor arms  922  are connected to a central hub which in turn is connected to tension element  924 . 
       FIG. 10A  shows a distal end view of an anchor comprising a spiral element having a three dimensional shape. Anchor  1000  comprises a three dimensional spiral element  1002 . Diameter of spiral element  1002  may be substantially constant or may substantially vary along the length of spiral element  1002 . Spiral element  1002  may be made of an elastic, super-elastic or shape memory materials. Spiral element  1002  may be made of a variety of materials including, but not limited to metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; polymers e.g. polypropylene, Teflon etc.; synthetic fibers e.g. various grades of Nylon, polyethylene, polypropylene, polyester, Aramid etc.; natural fibers e.g. cotton, silk etc.; rubber materials e.g. various grades of silicone rubber etc. Spiral element  1002  is connected to a central hub  1004 , which in turn is connected to a tension element. In one embodiment, spiral element  1002  is directly connected to a tension element without using central hub  1004 . FIG.  10 A′ shows a side view of the anchor in  FIG. 10A . FIG.  10 A′ shows anchor  1000  comprising spiral element  1002  connected to central hub  1004  which in turn is connected to a tension element  1006 .  FIG. 10B  shows a distal end view of an anchor comprising a spiral element having a two dimensional shape. Anchor  1000  comprises a two dimensional spiral element  1010 . Spiral element  1010  may be made of an elastic, super-elastic or shape memory materials. Spiral element  1010  may be made of a variety of materials including, but not limited to metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; polymers e.g. polypropylene, Teflon etc.; synthetic fibers e.g. various grades of Nylon, polyethylene, polypropylene, polyester, Aramid etc.; natural fibers e.g. cotton, silk etc.; rubber materials e.g. various grades of silicone rubber etc. Spiral element  1010  is connected to a central hub  1012  which in turn is connected to a tension element. In one embodiment, spiral element  1010  is directly connected to a tension element without using central hub  1012 . FIG.  10 B′ shows a side view of the anchor in  FIG. 10B . FIG.  10 B′ shows anchor  1008  comprising spiral element  1010  connected to central hub  1012  which in turn is connected to a tension element  1014 .  FIG. 10C  shows a distal end view of an anchor comprising one or more circular elements. In  FIG. 10C , anchor  1016  comprises an inner circular element  1018  and an outer circular element  1020 . A series of radial arms or struts  1022  connect inner circular element  1018  to outer circular element  1020  and to a central hub  1024 . Central hub  1024  may have a lumen  1026 . Anchor  1016  may be substantially two dimensional or three dimensional. FIG.  10 C′ shows a perspective view of the anchor in  FIG. 10C . FIG.  10 C′ shows an anchor  1016  comprising an inner circular element  1018 , an outer circular element  1020  and series of radial arms or struts  1022  connecting inner circular element  1018  to outer circular element  1020  and to a central hub  1024 . Central hub  1024  is connected to a tension element. 
       FIG. 10D  shows a perspective view of an embodiment of an anchoring device comprising an outer ring. Anchor  1040  comprises a central hub  1042  and an outer ring  1044 . In one embodiment, central hub  1042  acts as a plug to plug an opening in the anatomy to reduce or prevent bleeding or leakage of fluids. Central hub  1042  is connected to outer ring  1044  by one or more bars or struts  1046 . In one embodiment, central hub  1042  is connected to an inner ring  1048  which in turn is connected to outer ring  1044  by one or more bars or struts  1046 . Central hub  1042  further comprises a locking element  1050 . Locking element  1050  comprises a lumen  1052  through which a tension element can slide. After positioning anchor  1040  in a desired position with respect to the tension element, locking element  1050  is used to securely attach anchor  1040  on the tension element. Locking element  1050  may comprise a design disclosed including various locking designs disclosed elsewhere in this patent application. Anchor  1040  may be made from a variety of materials including, but not limited to synthetic fibers e.g. various grades of Nylon, polyethylene, polypropylene, polyester, Aramid etc.; metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; natural fibers e.g. cotton, silk etc.; rubber materials e.g. various grades of silicone rubber etc. 
       FIG. 10E  shows a partial perspective view of an anchoring device comprising a hemostatic element. Anchor  1060  comprises a central hub  1062 . In one embodiment, central hub  1062  acts as a plug to plug an opening in the anatomy to reduce or prevent bleeding or leakage of fluids. Central hub  1062  comprises a cinching mechanism to allow central hub  1062  to cinch on to a tension element  1064  passing through central hub  1062 . The free end  1066  of tension element  1064  is severed to minimize the presence of tension element  1064  in the anatomy. Anchor  1060  further comprises an outer ring  1068 . Central hub  1062  is connected to outer ring  1068  by one or more struts  1070 . Anchor  1060  further comprises a mesh or porous element  1072  between outer ring  1068  and struts  1070 . The mesh or porous element  1072  may be concave shaped as shown in  FIG. 10E . Mesh or porous element  1072  allows for tissue ingrowth over a period of time thus providing additional securing of anchor  1060  to tissue. 
       FIG. 11A  shows a perspective view of a device having a set of anchors comprising a curved sheet. Anchoring device  1100  may comprise one or more anchors comprising a curved sheet. In this example, anchoring device  1100  comprises a first anchor  1102  and a second anchor  1104 . First anchor  1102  and second anchor  1104  may comprise elastic, super elastic or shape memory materials. First anchor  1102  and second anchor  1104  may be made from various materials including, but not limited to metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; polymers e.g. polypropylene, Teflon etc.; synthetic fibers e.g. various grades of Nylon, polyethylene, polypropylene, polyester, Aramid etc.; natural fibers e.g. cotton, silk etc.; rubber materials e.g. various grades of silicone rubber etc. The concave surface of first anchor  1102  is connected to a first end of a tension element  1106 . Second end of tension element  1106  is connected to the convex surface of second anchor  1104 . In one embodiment of a method to deploy anchoring device  1106 , first anchor  1102  is deployed out of an anatomical tissue (e.g. the prostate gland) into a first anatomical cavity (e.g. the pelvic cavity). Thereafter, second anchor  1104  is deployed into a second anatomical cavity (e.g. the urethral lumen). This method embodiment has the advantage of using the natural curvature of first anchor  1102  and second anchor  1104  to distribute pressure on first anchor  1102  and second anchor  1104  over a large area. 
       FIGS. 12A through 17I  show further examples of anchor designs and/or anchoring device designs.  FIG. 12A  shows a perspective view of an anchor comprising an arrowhead. Anchor  1200  comprises an arrowhead  1202 . Arrowhead  1202  may be made from various materials including, but not limited to metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; polymers e.g. polypropylene, Teflon etc.; rubber materials e.g. various grades of silicone rubber etc. Arrowhead  1202  may comprise a sharp distal tip. Arrowhead  1202  may have a three dimensional or a substantially two dimensional design. Proximal region of arrowhead  1202  is wider that the distal region of arrowhead  1202  to resist motion of arrowhead  1202  along the proximal direction after it is deployed in a tissue. Proximal region of arrowhead  1202  is connected to a tension element  1204 .  FIG. 12B  shows a crossectional view of an anchor comprising a cup-shaped element that encloses a cavity. Anchor  1208  comprises a cup-shaped element  1210 . Proximal, concave surface of cup-shaped element  1210  encloses a cavity. Cup-shaped element  1210  may be made from various materials including, but not limited to metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; polymers e.g. polypropylene, Teflon etc.; rubber materials e.g. various grades of silicone rubber etc. Proximal region of cup-shaped element  1210  is connected to a tension element  1212 .  FIG. 12C  shows a perspective view of an anchor comprising a screw. Anchor  1216  comprises a screw  1218 . Screw  1218  may be made from various materials including, but not limited to metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; polymers e.g. polypropylene, Teflon etc. Screw  1218  may comprise a sharp distal tip. Proximal region of screw  1218  may be wider that the distal region of screw  1218  to resist motion of screw  1218  along the proximal direction after it is deployed in a tissue. Screw  1218  comprises a thread rolled thread including, but not limited to wood screw style thread, double lead thread, tapping style thread, tapered wood thread etc. Proximal region of arrowhead  1202  is connected to a tension element  1204 . 
       FIGS. 13A and 13B  show perspective views of an uncollapsed state and a collapsed state respectively of an anchor comprising a collapsible region. In  FIG. 13A , anchor element  1300  is in an uncollapsed state. Anchor element  1300  comprises a hollow shaft  1302  comprising one or more collapsible regions. A collapsible region comprises one or more windows  1304 . Windows  1304  are cut in hollow shaft  1302  in such a way that several thin, collapsible struts  1306  are created between adjacent windows  1304 . In  FIG. 13B , anchor element  1300  is in a collapsed state. When anchor element  1300  is compresses along its length, collapsible struts  1306  are deformed in the radially outward direction to create one or more anchoring regions. 
       FIGS. 13C and 13D  show perspective views of an undeployed state and a deployed state respectively of an anchor comprising radially spreading arms. In  FIG. 13C , anchor  1312  comprises a hollow tube  1314 . Hollow tube  1314  is made from suitable elastic, super-elastic or shape memory materials such as metals including, but not limited to titanium, stainless steel, Nitinol etc.; suitable elastic polymers etc. U-shaped slots  1316  are cut in hollow tube  1314  in such a way that arms  1318  are created within U-shaped slots  1316 . In this embodiment, U-shaped slots are substantially parallel to the axis of hollow tube  1314 . In absence of an external force, arms  1318  tend to spread in a radially outward direction. Anchor  1312  is kept in an undeployed state by enclosing anchor  1312  in a sheath. Anchor  1312  is deployed by removing the sheath to allow arms  1318  to spread in a radially outward direction as shown in  FIG. 13D . 
     Hollow tube  1314  may comprise one or more cinching elements. Cinching elements may be located on the proximal region, distal region or a middle region of hollow tube  1314 . The cinching element or elements may comprise cinching mechanisms including, but not limited to cinching mechanisms disclosed in  FIGS. 26A through 29P . 
       FIG. 13E  shows perspective views of an alternate embodiment of an undeployed state of an anchor comprising radially spreading arms. In  FIG. 13C , anchor  1320  comprises a hollow tube  1322 . Hollow tube  1322  is made from suitable elastic, super-elastic or shape memory materials such as metals including, but not limited to titanium, stainless steel, Nitinol etc.; suitable elastic polymers etc. U-shaped slots  1324  are cut in hollow tube  1322  in such a way that arms  1326  are created within U-shaped slots  1324 . In this embodiment, U-shaped slots are at an angle to the axis of hollow tube  1322  as shown in  FIG. 13E . 
       FIGS. 14A and 14B  show perspective views of anchoring devices comprising an adhesive delivering element.  FIG. 14A  shows a perspective view of an anchoring device  1400  comprising a hollow shaft  1402  with a shaft lumen. Hollow shaft  1402  can be made of suitable biocompatible materials including, but not limited to Pebax, Polyimide, Braided Polyimide, Polyurethane, Nylon, PVC, Hytrel, HDPE, PEEK, metals like stainless steel and fluoropolymers like PTFE, PFA, FEP and EPTFE etc. Distal end of shaft lumen ends in a delivery opening  1404 . When an adhesive is injected through the shaft lumen, it emerges out of anchoring device  1400  through delivery opening  1404 . Hollow shaft  1402  may also comprise an attachment element  1406  such as a porous woven or non-woven circular sleeve securely attached to hollow shaft  1402 . The circular sleeve may be made of a variety of materials including, but not limited to metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; polymers e.g. polypropylene, Teflon etc.; synthetic fibers e.g. various grades of Nylon, polyethylene, polypropylene, polyester, Aramid etc.; natural fibers e.g. cotton, silk etc.; rubber materials e.g. various grades of silicone rubber etc. The adhesive flowing out through delivery opening comes into contact with attachment element  1406  and securely attaches attachment element  1406  to surrounding tissue.  FIG. 14B  shows a perspective view of an anchoring device  1408  comprising a hollow shaft  1410  with a shaft lumen. Hollow shaft  1410  can be made of suitable biocompatible materials including, but not limited to Pebax, Polyimide, Braided Polyimide, Polyurethane, Nylon, PVC, Hytrel, HDPE, PEEK, metals like stainless steel and fluoropolymers like PTFE, PFA, FEP and EPTFE etc. Distal end of shaft lumen ends in a delivery opening  1412 . When an adhesive is injected through the shaft lumen, it emerges out of anchoring device  1408  through delivery opening  1412 . Hollow shaft  1410  may also comprise an attachment element  1414  such as porous foam securely attached to hollow shaft  1410 . The porous foam may be made of a variety of materials including, but not limited to polymers e.g. polypropylene, Teflon etc.; synthetic fibers e.g. various grades of Nylon, polyethylene, polypropylene, polyester, Aramid etc.; rubber materials e.g. various grades of silicone rubber etc. The adhesive flowing out through delivery opening comes into contact with attachment element  1414  and securely attaches attachment element  1414  to surrounding tissue. Typical examples of adhesives that can be used with anchoring device  1400  and anchoring device  1408  include but are not limited to cyanoacrylates, marine adhesive proteins, fibrin-based sealants etc. 
       FIGS. 15A and 15B  show two configurations of an anchoring device comprising a ratcheted tension element. Anchoring device  1500  comprises a distal anchor. Distal anchor may comprise a design selected from the variety of designs disclosed elsewhere in this document. In this particular example, distal anchor comprises a series of radial arms  1502  connected to a central hub  1504 . The proximal end of central hub is attached to a ratcheted tension element  1506 . A proximal anchor is located on ratcheted tension element  1506  proximal to the distal anchor. Proximal anchor may comprise a design selected from the variety designs disclosed elsewhere in this document. In this particular example, distal anchor comprises a series of radial arms  1508  connected to a central hub  1510 . Central hub  8368  has a central lumen through which ratcheted tension element  1506  can slide. Ratcheted tension element  1506  has ratchets arranged such that proximal anchor can slide easily over ratcheted tension element  1506  in the distal direction but cannot slide easily in the proximal direction. In  FIG. 15B , proximal anchor slides over ratcheted tension element  1506  in the distal direction. This causes a compression of tissue between distal anchor and proximal anchor. The compression of tissue can be maintained since proximal anchor cannot slide easily in the proximal direction. In one embodiment of a method using anchoring device  1500 , distal anchor is introduced via an anatomical lumen (e.g. the urethral lumen) and through a tissue (e.g. the prostate gland) into an anatomical cavity (e.g. the pelvic cavity). Thereafter, proximal anchor is advanced along ratcheted tension element  1506  till it encounters a wall (e.g. the urethral wall) of the anatomical lumen. Anchoring device  1500  may be made from various materials including, but not limited to metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; polymers e.g. polypropylene, Teflon etc. 
       FIG. 16  shows a perspective view of an anchor comprising a trocar lumen. Anchor  1600  comprises a hollow shaft  1602  comprising a lumen. A trocar  1604  or a penetrating device can pass through hollow shaft  1602  such that the distal tip of trocar  1604  emerges out through the distal end of hollow shaft  1602 . Distal end of hollow shaft  1602  comprises a tapering region  1606  with a smaller distal diameter and a larger proximal diameter. Tapering region  1606  further comprises a series of sharp projections  1608  located on the proximal end of tapering region  1606 . Projections  1608  may be projecting in the proximal direction, radially outward direction etc. Projections  1608  prevent the movement of anchor  1600  in the proximal direction after it has penetrated through a tissue. Anchor  1600  may also comprise a sleeve  1610  located proximal to tapering region  1606 . Sleeve  1610  is made of a porous material that has a plurality of pores that allow for tissue ingrowth thus anchoring sleeve  1610  firmly in tissue. Sleeve  1610  may also help to distribute the pressure on tapering region  1606  over a wider area. Sleeve  1610  may be non-woven or woven. Sleeve  1610  can be made of variety of materials including, but not limited to synthetic fibers e.g. various grades of Nylon, polyethylene, polypropylene, polyester, Aramid etc.; metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; natural fibers e.g. cotton, silk etc.; rubber materials e.g. various grades of silicone rubber etc. 
       FIG. 17A  shows a perspective view in the undeployed state of an anchor comprising a rigid or partially flexible T element and a crumpling element. In  FIG. 17A , anchoring device  1700  comprises a distal, T element  1702 . The T element  1702  may be made of a variety of materials including, but not limited to metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; polymers e.g. polypropylene, Teflon etc.; rubber materials e.g. various grades of silicone rubber etc. Further it may be a composite material or have cut out sections to allow it to be flexible in certain dimensions but rigid in other dimensions. In this example, T element  1702  is in the form of a hollow cylinder. The proximal end of T element  1702  is in contact with the distal end of a delivery rod  1704 . Delivery rod  1704  is hollow and is used to deliver T element  8266  in a target anatomical region. A trocar  1705  can pass through delivery rod  1704  and through T element  1702  such that the distal tip of trocar emerges through the distal end of rigid element  1702 . The T-element could also be contained within a lumen of the trocar or may be the trocar itself. of the T element  1702  is connected to the distal end of a flexible tension element  1706 . Various connection means are possible such as the tension element being tied or crimped to the T element, or passing through a loop in the T element, or being adhered by adhesive or weld, or by being made of a continuous material which becomes the T element. Although the T element is shown as a T, any shape which is larger in at least one dimension compared to its other dimensions could appropriately be released and cause to change it&#39;s orientation to produce an anchoring effect. Examples of materials that can be used to manufacture tension element  1706  include but are not limited to synthetic fibers e.g. various grades of Nylon, polyethylene, polypropylene, polyester, Aramid etc.; metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; natural fibers e.g. cotton, silk etc.; rubber materials e.g. various grades of silicone rubber etc. A substantially flattened body  1708  is located on the distal region of tension element  1706 . Tension element  1706  is threaded through body  1708  in such a way that tension element  1706  can slide through body  1708 . Body  1708  may be non-woven or woven. Body  1708  can be made of a variety of materials including, but not limited to synthetic fibers e.g. various grades of Nylon, polyethylene, polypropylene, polyester, Aramid etc.; metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; natural fibers e.g. cotton, silk etc.; rubber materials e.g. various grades of silicone rubber etc. Body  1708  may have a variety of shapes including, but not limited to square, rectangular, triangular, other regular polygonal, irregular polygonal, circular etc. Body  1708  may have a substantially one dimensional, two dimensional or three dimensional shape.  FIGS. 17B and 17C  show various steps of a method to deploy the anchoring device shown in  FIG. 17A . In  FIG. 17B , anchoring device  1700  is introduced in an anatomical cavity (e.g. the pelvic cavity) through a tissue (e.g. the prostate gland). Thereafter, trocar  1705  is withdrawn by pulling trocar  1705  in the proximal direction. Thereafter, delivery rod  1704  is withdrawn by pulling delivery rod  1704  in the proximal direction. Thereafter, tension element  1706  is pulled in the proximal direction. Tension element  1706  in turn pulls T element  1702  in the proximal direction. In  FIG. 17C , rigid element  1702  is pulled against a wall of the tissue (e.g. the prostate gland) but is unable to penetrate the tissue because of its size. This causes body  1708  to crumple because of compression of body  1708  between the wall of the tissue and rigid element  1702 . Crumpled body  1708  may be designed to cause tissue ingrowth or epithelialization in body  1708  as well as healing, hemostasis or a more even force distribution. 
       FIGS. 17D and 17E  show perspective views of an undeployed and deployed configuration of an anchor comprising a rigid or partially flexible T element with one or more openings or perforations.  FIG. 17D  shows a perspective view of an anchoring device  1720  comprising an anchor  1722 . Anchor  1722  comprises a tubular body. The tubular body may comprise one or more openings or perforations  1724  in the tubular body. Openings or perforations  1724  increase the flexibility of anchor  1722 . This makes it easier to navigate anchoring device  1720  through the anatomy before reaching its target location. Further it enables anchoring device  1720  to be passed through a tight bend in the anatomy or through a delivery device. Within tubular body of anchor  1722  is trocar tip  1727  that is fixedly attached to tensioning element  1728 . In the embodiment shown in  FIG. 17D , anchor  1722  comprises a lumen. A length of the distal end of deployment element  1726  passes through the proximal end of the lumen and abuts trocar tip  1727  that enables anchor  1722  to puncture tissue. In an alternate embodiment trocar tip is fixedly attached to elongate deployment element  1726  and is retracted fully into element  1729  upon anchor deployment. In an alternate embodiment, distal tip of deployment device  1726  is not exposed through the distal end of anchor  1722 . Distal end of anchor  1722  comprises a sharp tip to enable anchor  1722  to puncture tissue. Anchoring element  1720  further comprises a tension element  1728  attached to tubular body  1722 . In this embodiment, distal end of tension element  1728  attached to the inner surface of the trocar tip  1727 . Proximal region of tension element  1728  passes through deployment element  1726 . Anchor  1722  is deployed by pushing in a distal direction one elongate deployment element  1726 , that runs within lumen of anchor  1722  abutting trocar tip  1727  distally, in tandem with another elongate deployment element  1729  that abuts the proximal end of anchor  1722 . Anchoring device  1720  punctures tissue to transport anchor  1722  through a first anatomical location (e.g. a prostate gland) to a second anatomical location (e.g. the pelvic cavity, urethra etc.). Thereafter, deployment element  1726  is withdrawn by pulling deployment element  1726  in the proximal direction. Thereafter, tension element  1728  is pulled in the proximal direction. This causes anchor  1722  to anchor in tissue as shown in  FIG. 17E . Proximal portion of tension element  1728  emerges out of anchor  1722  through a lengthwise groove in anchor  1722  to create a T shaped anchor as shown in  FIG. 17E . Tension on tensioning element  1728  causes trocar tip  1727  to retract into lumen  1722 . In the example shown, the first anatomical location is the prostate gland PG and the second anatomical location is the pelvic cavity. Anchoring device  1720  can be made from a variety of materials including, but not limited to metals such as synthetic fibers e.g. various grades of Nylon, polyethylene, polypropylene, polyester, Aramid etc.; metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; natural fibers e.g. cotton, silk etc.; rubber materials e.g. various grades of silicone rubber etc. Tension element  1728  may then be connected to any one of the other anchoring elements such as anchor  10 D. 
       FIGS. 17F and 17G  show perspective views of an undeployed and deployed configuration of an anchor comprising a stent. Anchor  1730  comprises a self-expanding stent  1732  and a tension element  1734 . Distal end of tension element  1734  is attached to stent  1732 . In one embodiment, distal end of tension element  1734  is attached on the mid section of stent  1732 . Stent  1732  may comprise various designs including, but not limited to metallic tube designs, polymeric tube designs, spiral designs, chain-linked designs, rolled sheet designs, single wire designs etc. Stent  1732  may have an open celled or closed celled structure. A variety of fabrication methods can be used for fabricating stent  1732  including but not limited to laser cutting a metal or polymer element, welding metal elements etc. A variety of materials can be used for fabricating stent  1732  including but not limited to metals, polymers, foam type materials, super elastic materials etc. A variety of features can be added to stent  1732  including but not limited to radiopaque coatings, drug elution mechanisms etc. Anchor  1730  is introduced through a sheath  1736  into a target anatomy. Thereafter, sheath  1736  is withdrawn. This causes stent  1732  to revert to its natural shape as shown in  FIG. 17G  and act as an anchor. 
       FIGS. 17H and 17I  show perspective views of an undeployed and deployed configuration of an anchor comprising a spring. Anchor  1740  comprises an elastic spring  1742  and a tension element  1744 . Distal end of tension element  1744  is attached to spring  1742 . In one embodiment, distal end of tension element  1744  is attached on the mid section of spring  1742 . A variety of materials can be used for fabricating spring  1742  including but not limited to metals, polymers, foam type materials, super elastic materials etc. A variety of features can be added to spring  1742  including but not limited to radiopaque coatings, drug elution mechanisms etc. Anchor  1740  is introduced through a sheath  1746  into a target anatomy to reduce the profile of spring  1742 . Thereafter, sheath  1746  is withdrawn. This causes spring  1742  to revert to its natural shape as shown in  FIG. 17I  and act as an anchor. 
       FIGS. 18A through 22E  show various embodiments of mechanisms to deploy one or more anchors.  FIG. 18A  shows a crossection of an anchor deploying mechanism comprising a screw system.  FIG. 18A  shows an anchor deploying mechanism comprising an anchor  1800  comprising an anchor body  1802  and anchoring elements  1804  attached to anchor body  1802 . Anchor body  1802  comprises an inner lumen. Inner lumen of anchor body  1802  comprises screw threading. Anchoring elements  1804  may have various designs including, but not limited to anchor designs disclosed elsewhere in this document. Anchor body  1802  and anchoring elements  1804  may be made of a variety of materials including, but not limited to metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; polymers e.g. polypropylene, Teflon etc.; rubber materials e.g. various grades of silicone rubber etc. The anchor deploying mechanism further comprises a deploying shaft  1806 . Distal region of deploying shaft  1806  comprises a screw threading such that deploying shaft  1806  can be screwed into anchor body  1802 .  FIG. 18B  shows the method of deploying an anchor comprising a screw mechanism. Deploying shaft  1806  is rotated to release the distal region of deploying shaft  1806  from anchor body  1802  after positioning anchor  1800  in a desired location. Such a mechanism can be used to deploy one or more anchors. In one embodiment, more than one anchors are located on deploying shaft  1806 . The anchors can be sequentially deployed by rotating deploying shaft  1806 . Deploying shaft  1806  may be made of a variety of materials including, but not limited to metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; polymers e.g. polypropylene, Teflon etc. In one embodiment, the anchor deploying mechanism is located inside an outer sheath. 
       FIGS. 19A and 19B  show a crossectional view of an anchor deploying system comprising an electrolytic detachment element.  FIG. 19A  shows a crossection of an anchor deploying mechanism comprising a deployable anchor  1900 . Deployable anchor  1900  comprises an anchor body  1902  and anchoring elements  1904  attached to anchor body  1902 . Anchoring elements  1904  may have various designs including, but not limited to anchor designs disclosed elsewhere in this document. Anchor body  8402  and anchoring elements  8404  may be made of a variety of materials including, but not limited to metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; polymers e.g. polypropylene, Teflon etc.; rubber materials e.g. various grades of silicone rubber etc. Proximal region of deployable anchor  1900  further comprises an electrolyzable element  1906 . Electrolyzable element  1906  is made of a length of metallic wire e.g. steel wire. Proximal region of electrolyzable element  1906  is electrically connected to a deploying shaft  1908 . Proximal region of deploying shaft  1908  is further connected to a first electrode. The anchor deploying system further comprises a second electrode  1910  connected to a bodily region of the patient to be treated. In  FIG. 19B , the first electrode is connected to a positive terminal of a power supply and the second electrode is connected to the negative terminal of the power supply to form an electrical circuit. Electrical current flowing between electrolyzable element  1906  and second electrode  1910  causes metallic ions from electrolyzable element  1906  to dissolve into surrounding anatomy. This causes electrolyzable element  1906  to detach from deploying shaft  1908 . 
       FIG. 20  shows a perspective view of an anchor deploying system comprising a looped ribbon. The anchor deploying system comprises a deployable anchor  2000 . Deployable anchor  2000  comprises an anchor body  2002  and anchoring elements  2004  attached to anchor body  2002 . Anchoring elements  2004  may have various designs including, but not limited to anchor designs disclosed elsewhere in this document. Anchor body  2002  and anchoring elements  2004  may be made of a variety of materials including, but not limited to metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; polymers e.g. polypropylene, Teflon etc.; rubber materials e.g. various grades of silicone rubber etc. Proximal region of deployable anchor  2000  further comprises a looping lumen  2006 . A looped ribbon  2008  is looped through looping lumen  2006 . Looped ribbon  2008  may be made of a variety of materials including, but not limited to synthetic fibers e.g. various grades of Nylon, polyethylene, polypropylene, polyester, Aramid etc.; metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; natural fibers e.g. cotton, silk etc.; rubber materials e.g. various grades of silicone rubber etc. looped ribbon  2008  extends to a proximal region where it can be cut by a user. In a method of deploying deployable anchor  2000 , a single cut is made in looped ribbon  2008  at a proximal region. This turns looped ribbon  2008  into a straight ribbon. The straight ribbon can then be pulled in the proximal direction to remove it from deployable anchor  2000 . Looped ribbon  2008  may also be in the form of a looped monofilament or multifilament wire or suture. 
       FIG. 21A  shows a crossectional view of an anchor deploying system comprising a locked ball. The anchor deploying system comprises a deployable anchor  2100 . Deployable anchor  2100  comprises an anchor body  2102 . Deployable anchor  2100  may have various designs including, but not limited to anchor designs disclosed elsewhere in this document. Proximal end of anchor body  2102  is connected to a thin shaft  2104 . Proximal end of thin shaft  2104  comprises a locking ball  2106 . Anchor body  8428 , thin shaft  2104  and locking ball  2106  may be made of a variety of materials including, but not limited to metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; polymers e.g. polypropylene, Teflon etc.; rubber materials e.g. various grades of silicone rubber etc. The anchor deploying system further comprises an outer locking sheath  2108 . Distal end of locking sheath  2108  comprises an opening  2110 . Diameter of opening  2110  is greater than the diameter of thin shaft  2104  but greater than diameter of locking ball  2106 . Thus, locking ball  2106  is locked in locking sheath  2108 . The anchor deploying system further comprises a deploying shaft  2112  located within locking sheath  2108 . Deploying shaft  2112  can be pushed in the distal direction within locking sheath  2108  by a user. Locking sheath  2108  and deploying shaft  2112  may be made of a variety of materials including, but not limited to metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; polymers e.g. polypropylene, Teflon etc. In one embodiment, distal region of locking sheath  2108  comprises one or more longitudinal grooves or windows to allow distal region of locking sheath  2108  to expand easily in the radial direction.  FIGS. 21B and 21C  show a method of deploying an anchor comprising a locked ball. In  FIG. 21B , deploying shaft  2112  is pushed in the distal direction by a user. This causes distal end of deploying shaft  2112  to push locking ball  2106  in the distal direction. This in turn causes locking ball  2106  to exert a force on the distal end of locking sheath  2108 . This force causes opening  2110  to enlarge and release locking ball  2106 . In  FIG. 21C , locking ball  2106  is released by locking sheath  2108  thus releasing deployable anchor  2100 . 
       FIGS. 22A through 22C  show various views of an anchor deploying system comprising two interlocking cylinders. The anchor deploying system comprises a proximal interlocking cylinder and a distal interlocking cylinder. The distal interlocking cylinder is located on an anchor to be deployed.  FIG. 22A  shows a perspective view of a proximal interlocking cylinder  2200  comprising a locking element  2202  located on the distal end of proximal interlocking cylinder  2200 . In this example, locking element  2202  comprises a solid cylinder with a ninety degree bend. Proximal interlocking cylinder  2200  and locking element  2202  may be made of a variety of materials including, but not limited to metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; polymers e.g. polypropylene, Teflon etc.  FIG. 22B  shows a crossectional view of the anchor deploying system comprising proximal interlocking cylinder  2200  interlocked with a distal interlocking cylinder  2204 . Distal interlocking cylinder  2204  comprises a groove  2206  which locks locking element  2202 . Locking element  2202  can be unlocked from distal interlocking cylinder  2204  by turning proximal interlocking cylinder  2200 . distal interlocking cylinder  2204  may be made of a variety of materials including, but not limited to metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; polymers e.g. polypropylene, Teflon etc.; rubber materials e.g. various grades of silicone rubber etc.  FIG. 22C  shows a crossectional view through plane A-A in  FIG. 22B .  FIG. 22C  shows distal interlocking cylinder comprising groove  2206 . Also shown is locking element  2202  located in groove  2206 . Turning proximal interlocking cylinder  2200  turns locking element  2202 . At a particular orientation, distal region of locking element  2202  can pass easily through groove  2206  unlocking proximal interlocking cylinder  2200  from distal interlocking cylinder  2204 . 
       FIGS. 22D and 22E  show the steps of a method of unlocking the two interlocking cylinders from the anchor deploying systems of  FIGS. 22A through 22C . In  FIG. 22D , locking element  2202  of proximal interlocking cylinder  2200  is locked in groove  2206  of distal interlocking cylinder  2204 . In  FIG. 22E , proximal interlocking cylinder  2200  is turned in a clockwise or counterclockwise direction to unlock locking element  2202  from groove  2206 . Thereafter, proximal interlocking cylinder  2200  is pulled in the proximal direction to separate proximal interlocking cylinder  2200  from distal interlocking cylinder  2204 . 
       FIG. 23A  shows a perspective view of a distal end of an anchoring device that has an imaging modality. Anchoring device  2300  comprises an elongate shaft  2302  comprising a lumen. Elongate shaft  2302  can be made of suitable biocompatible materials such as metals, polymers etc. The lumen of shaft  2302  terminates in a window  2304  located on the distal region of shaft  2302 . Anchoring device further comprises an imaging modality such as a cystoscope, an ultrasound imaging system etc. In this example, the imaging modality is a cystoscope  2306 . Distal end of cystoscope  2306  is located in window  2304  to allow visualization of the anatomy adjacent to window  2304 . In one embodiment, cystoscope  2306  is permanently fixed to anchoring device  2300 . In another embodiment, cystoscope  2306  can be introduced through the proximal region of anchoring device  2300 . Anchoring device  2300  further comprises a puncturing device  2308 . Puncturing device  2308  comprises a sharp distal tip and a lumen that holds an anchor. Anchoring device  2300  further comprises an anchor deployment device  2310 . Distal end of anchor deployment device  2310  is detachably attached to the anchor. 
       FIGS. 23B through 23G  show various steps of a method for compressing an anatomical region using the anchoring device of  FIG. 23A . In  FIG. 23B , Anchoring device  2300  is introduced in an anatomical region such that distal end of anchoring device  2300  is located adjacent to a target anatomical region to be treated. In one method embodiment, anchoring device  2300  is introduced transurethrally into the prostatic urethra. Thereafter, puncturing device  2308  is advanced to puncture the anatomical region. In this example, puncturing device  2308  punctures the prostate gland PG such that distal end of puncturing device  2308  is located in the pelvic cavity. Puncturing device comprises an anchor located in the lumen of puncturing device  2308 . The anchor comprises a distal anchor  2312 , a tension element  2314  connected at one end to distal anchor  2312  and a proximal anchor  2316  that can slide over tension element  2314 . Puncturing device  2308  comprises a groove at the distal end such that tension element exits puncturing device  2308  through the groove. Puncturing device  2308  further comprises a pusher  2318  that can push distal anchor  2312  out of puncturing device  2308 . Proximal anchor  2316  is detachably attached to the distal region of anchor deployment device  2310 . Proximal anchor  2312 , distal anchor  2316  and tension element  2314  may comprise designs including, but not limited to the designs disclosed elsewhere in this patent application. The imaging modality may be used to verify the accurate placement and working of anchoring device  2300 . In  FIG. 23C , pusher  2318  is pushed in the distal direction to push distal anchor  2312  out of puncturing device  2308 . Distal anchor  2312  is thus deployed in the anatomy e.g. in the pelvic cavity surrounding the prostate gland PG. Thereafter, in step  23 D, Puncturing device  2308  is withdrawn by pulling it in the proximal direction. In step  23 E, tension element  2314  is pulled in the proximal direction through anchor deployment device  2310 . Thereafter, in step  23 F, tension element  2314  is pulled further in the proximal direction such that the anatomical region between proximal anchor  2316  and distal anchor  2312  is compressed. Thereafter, in step  23 G, proximal anchor  2316  is securely locked on to tension element  2314 . Further in step  23 G, proximal anchor  2316  is detached from anchor deployment device  2310 . The detachment can be performed by a variety of mechanisms including, but not limited to the anchor detachment mechanisms disclosed elsewhere in this patent application. Further in step  23 G, excess length of tension element  2314  is removed. This removal can be done using a variety of methods including, but not limited to the methods disclosed elsewhere in this patent application such as cutting, delinking, melting, and breaking. Thereafter, anchoring device  2300  is withdrawn from the anatomy. It should be understood that these deployment steps may be repeated in the same, opposing or neighboring tissues to essentially tack up the encroaching tissue (i.e. prostatic tissue, tumor, relaxed tissue, expanded tissue or growth). It may be desired that over time both anchors become completely embedded within the tissue and covered to prevent encrustation, clotting or other tissue or body-fluid interaction—this may be facilitated by the processes, therapeutic agents and coatings described elsewhere in the application. Although these anchors are shown on either side of the tissue, it may be possible to deploy either or both of them within the body of the tissue itself to help bury them and eliminate the possibility that they may interact with other parts of the body. It should further be noted that in the case of application to the prostate, that this technique may be used on any of the lateral or middle lobes to compress or hold the prostate gland PG away from the lumen of the urethra. 
     If removal of the intra or para luminal anchor is required, it may be possible to resect that region completely, capturing the anchor embedded within the tissue and removing it en-bloc, severing the tether in the process. In the case of prostate applications, such removal may be accomplished with a standard resectoscope system. In other regions, and energized RF or sharp curette or blade may be used to resect the anchor minimally invasively. Alternatively if engagement with the locking mechanism is still achievable, it may be possible to simply unlock the tether, releasing the anchor. Lastly, if applying additional tension at some point after the procedure is required, it may be possible to engage and grasp the tether as it exits the locking device in the anchor and apply additional tension. 
     FIGS.  24 A through  24 C′ show various steps of a method of compressing an anatomical region using a device with deploying arms deployed through a trocar. In  FIG. 24A , an anchoring device  2400  is introduced in an anatomical region. Anchoring device  2400  comprising a distal anchor  2402  is introduced in the anatomy. Distal anchor  2402  comprises a hollow shaft. Distal end of distal anchor  2402  comprises one or more outwardly curling or spreading arms  2404 . Curling or spreading arms  2404  are made of an elastic, springy, super-elastic or shape memory material such that they tend to curl or spread in a radially outward direction in absence of an external force. Anchoring device  2400  further comprises a proximal anchor comprising a variety of designs including, but not limited to the designs disclosed elsewhere in this patent application. In this example, proximal anchor is designed similar to anchor  1040  in  FIG. 10D . Anchor  1040  can slide along proximal region of distal anchor  2402 . Anchor  1040  can also be attached to distal anchor  2402  after a desired positioning between anchor  1040  and distal anchor  2402  is achieved. Anchoring device  2400  is delivered through a trocar  2406 . Trocar  2406  comprises a sharp distal tip  2408  that can penetrate through tissue. The proximal region of distal tip  2408  comprises one or more grooves or notches such that distal ends of curling or spreading arms  2404  can be temporarily held together by distal tip  2408  to allow for easy introduction into a target anatomy. Anchoring device  2400  is introduced into a target tissue to be compressed such that curling or spreading arms  2404  are distal to the target tissue and anchor  1040  is proximal to the target tissue. FIG.  24 A′ shows the distal end view of the anchoring device  2400 . In  FIG. 24B , trocar  2406  is pushed in the distal direction relative to proximal anchor  2402 . This releases the distal ends of curling or spreading arms  2404  causing them to curl or spread outwards. FIG.  24 A′ shows the distal end view of the anchoring device  2400  with released curling or spreading arms  2404 . In  FIG. 24C , anchor  1040  is pushed in the distal direction over distal anchor  2402  to compress tissue between anchor  1040  and distal anchor  2402 . Thereafter, anchor  1040  is attached to the hollow shaft of distal anchor  2402 . Thereafter trocar  2406  is withdrawn from the anatomy. In the above embodiment, the tethering function is performed by the shaft of the distal anchor, and the force is created by the curling arms. This tension may be pre-set into the arms through heat forming. It should be noted that any mechanism capable of expanding from within a tubular shape and capable of applying retrograde forces on the tissue are within the scope of this invention such as expandable flanges, balloons, cages, molly-bolt-like structures, stent-like structures and springs. 
       FIG. 24D  shows a crossection through the deployed anchoring device  2400  of  FIG. 24A . 
     In one anchoring device embodiment, anchoring device  2400  comprises a distal anchor such as the distal anchor described in  FIG. 17A  instead of distal anchor  2412 . 
       FIG. 25A  shows a perspective view of a spring clip that can be used to spread the anatomy. Clip  2500  comprises two or more spreading arms  2502 . Spreading arms  2502  may be curved or straight. Distal ends of spreading arms  2502  may comprise a flattened region. The proximal ends or curved arms  2502  are connected to each other by a heel region  2504 . Heel region  2504  may be made from the same material as curved arms  2502 . In an undeployed configuration, spreading arms  2502  are held close to each other. When clip  2500  is deployed, spreading arms  2502  tend to expand away from each other thus spreading the anatomical region or regions between spreading arms  2502 . Clip  2500  can be made of suitable elastic, super-elastic or shape memory biocompatible materials including, but not limited to synthetic fibers e.g. various grades of Nylon, polyethylene, polypropylene, polyester, Aramid etc.; metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, etc. 
       FIGS. 25B through 25F  show various steps of a method of spreading an anatomical region or regions using the spring clip of  FIG. 25A . In  FIG. 25B , a delivery tool  2506  comprising a clip  2500  is introduced in the anatomy and positioned near the target anatomy to be spread. Delivery tool  2506  comprises an elongate hollow body  2508  comprising a lumen. Distal end of body  2508  may comprise a blunt, atraumatic end. Distal region of body  2508  comprises a slot  2510  that is in fluid communication with the lumen of body  2508 . Delivery tool may further comprise an outer sheath  2512  and an imaging modality  2514 . Imaging modality  2514  may be permanently attached to delivery tool  2506  or may be introduced into delivery tool  2506  by a user. In this example, imaging modality  2514  is a cystoscope. In  FIG. 25C , clip  2500  is introduced into the anatomy by pushing clip  2500  out of slot  2510  such that the distal ends of spreading arms  2502  emerge first. Slot  2510  is designed such that spreading arms  2504  are biased towards each other as they emerge out of slot  2510 . In  FIG. 25D , clip  2500  is further advanced such that distal tips of spreading arms  2502  penetrate into the tissue to be spread. In  FIG. 25E , clip  2500  is advanced further such that the biasing forces on spreading arms  2502  are removed. Spreading arms  2502  tend to spread away from each other thus spreading the tissue between them. Clip  2500  is detachably attached to delivery tool  2506  by a detaching mechanism  2516  including, but not limited to the several detaching mechanisms disclosed elsewhere in this patent application. In  FIG. 25F , detaching mechanism  2516  is used to detach clip  2500  from delivery tool  2506  or deploy clip  2500  in the target anatomy. In this example, distal region of delivery tool  2506  is inserted transurethrally into the prostatic urethra. Clip  2500  is then delivered into the anterior commissure to spread the two lateral lobes of the prostate gland PG apart. In one method embodiment, an opening in the commissure is made prior to the method of  FIGS. 25B through 25G . In another embodiment, the spreading force exerted by spreading arms  2502  cause cutting of the anterior commissure. Clip  2500  may be placed completely sub-urethrally or a small amount of heel region  2504  remains in the urethra. 
     The embodiments of anchoring devices wherein a sliding anchor is slid over a tension element may comprise one or more cinching elements. These cinching elements may be present on the sliding anchors, on the tension elements etc. A cinching element may be a separate device that cinches to a tension element. In doing so, it increases the effective diameter of that region of the tension element and prevents the tension element from sliding through a sliding anchor. Cinching elements may allow only unidirectional motion of the sliding anchor over the tension element or may prevent any substantial motion of the sliding anchor over the tension element. Typical examples of such cinching mechanisms include, but are not limited to mechanisms described in the  FIG. 26  series. For example,  FIGS. 26A and 26B  show a crossectional view and a perspective view respectively of a mechanism of cinching a tension element or tether to an anchor. In  FIG. 26A , cinching mechanism  2600  comprises an outer base  2602 . Outer base  2602  comprises one or more grooves created by the presence of two or more leaflets  2604 . Leaflets  2604  are biased along a first axial direction as shown in  FIG. 26A . When a tension element  2606  is located in the one or more grooves, cinching mechanism  2600  allows motion of tension element  2606  only along the first axial direction and prevents substantial movement of tension element  2606  in the opposite direction. 
       FIGS. 26C and 26D  show a partial section through a cinching mechanism comprising a cam element. In  FIG. 26C , cinching mechanism  2610  comprises an outer body  2612  made of suitable biocompatible metals, polymers etc. Body  2162  comprises a cam  2614  located on a pivot  2616 . Cam  2614  may comprise a series of teeth to grip a tension element  2618  passing through body  2612 . In one embodiment, body  2162  comprises an opening  2620  located proximal to cam  2614 . Proximal region of tension element  2618  passes out of body  2612  through opening  2620 . Cinching mechanism  2610  allows movement of body  2162  over tension element  2618  in the proximal direction. In  FIG. 26D , body  2162  is moved over tension element  2618  in the distal direction. Motion of tension element  2618  over cam  2614  causes cam  2614  to turn in the anti-clockwise direction. This causes tension element  2618  to be pinched between cam  2614  and body  2612 . This in turn prevents further motion of body  2162  over tension element  2618 . 
       FIG. 26E  shows a sectional view of an embodiment of a cinching mechanism comprising a locking ball. Cinching mechanism  2630  comprises an outer body  2632  comprising a lumen. A tension element  2634  passes through the lumen of outer body  2632 . The lumen of outer body gradually reduces in the proximal direction as shown in  FIG. 26E . A locking ball  2636  is present in the lumen. Motion of outer body  2632  over tension element  2634  in the distal direction pushes locking ball  2636  in the proximal region of outer body  2632 . A proximal end region  2638  of a small diameter prevents locking ball  2636  from falling out of outer body  2632 . The large lumen diameter in the proximal region of outer body  2632  allows free motion of locking ball  2636 . Thus, presence of locking ball  2636  does not hinder the motion of outer body  2632  over tension element  2634  in the proximal direction. When outer body  2632  is moved over tension element  2634  in the proximal direction, locking ball  2636  is pushed in the distal region of outer body  2632 . The small lumen diameter in the proximal region of outer body  2632  constricts motion of locking ball  2636 . This causes a region of tension element  2634  to be pinched between anchoring ball  2636  and outer body  2632 . This in turn prevents further motion of outer body  2632  over tension element  2634  in the proximal direction. This mechanism thus allows unidirectional motion of outer body  2632  is over tension element. 
       FIG. 26F  shows a side view of an embodiment of a cinching mechanism comprising multiple locking flanges. In this embodiment, cinching mechanism  2644  comprises a body  2646  comprising a lumen lined by a first locking flange  2648  and a second locking flange  2650 . First locking flange  2648  and second locking flange  2650  are biased in the proximal direction as shown. A tension element  2652  passes through the lumen of body  2646 . First locking flange  2648  and second locking flange  2650  together allow the movement of body  2646  over tension element  2652  in the distal direction, but prevent movement of body  2646  over tension element  2652  in the proximal direction. Similar cinching mechanisms may be designed comprising more than two locking flanges.  FIG. 26G  shows an end view of body  2646  comprising a lumen lined by first locking flange  2648  and second locking flange  2650 . Body  2646  may be made of suitable biocompatible metals, polymers etc. 
       FIG. 26H  shows a side view of an embodiment of a cinching mechanism comprising a single locking flange. In this embodiment, cinching mechanism  2656  comprises a body  2658  comprising a lumen lined by a locking flange  2660 . Locking flange  2660  is biased in the proximal direction as shown. A tension element  2662  passes through the lumen of body  2658 . Locking flange  2660  allows the movement of body  2658  over tension element  2662  in the distal direction, but prevents movement of body  2658  over tension element  2662  in the proximal direction.  FIG. 26I  shows an end view of body  2658  comprising a lumen  2662  lined by locking flange  2660 . Body  2658  may be made of suitable biocompatible metals, polymers etc. 
       FIG. 26J  shows an end view of a cinching mechanism comprising a crimping lumen. Cinching mechanism  2670  comprises a body  2672  comprising a crimping lumen  2674 . Crimping lumen  2674  is in the form of an arc with a gradually reducing size as shown in  FIG. 26J . A tension element  2676  passes through crimping lumen  2674 . In  FIG. 26J , tension element  2676  is locked in a region of crimping lumen  2674  of a diameter smaller than the diameter of tension element  2676 . Tension element  2676  can be unlocked from crimping lumen  2674  by rotating body  2672  in the anti-clockwise direction. Similarly, rotating body  2672  in the clockwise direction causes an unlocked tension element  2676  to be locked into crimping lumen  2674 . 
     In an alternate embodiment, cinching mechanism comprises a disk shaped body comprising a central lumen. Central lumen is large enough to allow a tension element to slide easily through the central lumen. One or more radially oriented slits emerge from the central lumen. The radially oriented slits have a diameter that is of the same size or is slightly smaller than the diameter of the tension element. To lock cinching mechanism to the tension element, the tension element is forced through one of the radially oriented slits. The friction between the disk shaped body and the tension element prevents or resists sliding of tension element through the disk shaped body. To unlock cinching mechanism from the tension element, the tension element is moved back to the central lumen. 
     In another alternate embodiment, cinching mechanism comprises a disk shaped body comprising a small central lumen. The central region of the body comprises three or more triangular flaps biased together out of the plane of the body. The ends of the triangular flaps together form the central lumen that is of the same size or is slightly smaller than the diameter of the tension element. Tension element can pass easily through the central lumen in the direction of the bias of the triangular flaps. But, tension element cannot pass or encounters substantial resistance when the tension element is pulled through the central lumen in the opposite direction. 
       FIGS. 26K and 26L  show crossections of an embodiment of a cinching mechanism comprising a crimping anchor in the undeployed and deployed configurations respectively. Cinching mechanism  2680  comprises a crimping anchor  2680  comprising a lumen. Crimping anchor  2680  can be made of a variety of biocompatible materials including, but not limited to metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc., polymers, etc. A tension element  2684  passes through the lumen of crimping anchor  2680 . The lumen of an undeployed crimping anchor  2680  is larger than the diameter of tension element  2684 . In  FIG. 26L , crimping anchor  2680  is deployed by compressing the middle section of crimping anchor  2680  such that crimping anchor  2680  compresses tension element  2684 . Friction between crimping anchor  2680  and tension element  2684  prevents relative motion between crimping anchor  2680  and tension element  2684 . Crimping anchor  2680  may be a component of a sliding anchor or may be a stand-alone device used to prevent or restrict motion of a sliding anchor over a tension element. 
       FIG. 26M  shows a perspective view of an embodiment of a cinching mechanism comprising an element providing a tortuous path to a tension element. In this example, cinching mechanism  2686  comprises a spring  2688 . A tension element  2690  is passed through spring  2688  such that the path of tension element  2690  through spring  2688  is tortuous. When spring  2688  is moved over tension element, motion of tension element  2690  through the tortuous path generates high frictional forces that prevent or reduce motion of spring  2688  over tension element  2690 . The frictional forces are strong enough to resist motion of spring  2688  over tension element  2690  after deploying cinching mechanism  2686  in the anatomy. A user can move spring  2688  over tension element  2690  by applying a force that overcomes the resistive frictional forces that prevent movement of spring  2688  over tension element  2690 . Similarly, other cinching mechanisms comprising a tortuous path can be used instead of spring  2688 . Examples of such mechanisms are solid elements comprising tortuous lumens, elements comprising multiple struts or bars that provide a tortuous path etc. In another embodiment the cinching mechanism comprises a knot on one or more tensioning element. Said knot can be advanced fully tightened or can be loose when advanced and tightened in situ. 
       FIG. 26N  shows a crossectional view of an embodiment of a locking mechanism comprising a space occupying anchor securely attached to a tension element. Locking mechanism  2692  comprises a hollow element  2694  comprising a lumen. Hollow element  2694  is a component of a sliding anchor that slides over tension element  2696 . Tension element  2696  comprises a space occupying anchor  2698  comprising a tapering distal end  2699 . Anchor  2698  is securely attached to tension element  2696 . Diameter of anchor  2698  is larger than the diameter of the lumen of hollow element. Due to this, anchor  2698  cannot pass through hollow element  2694  effectively locking the position of tension element  2696  with respect to the position of hollow element  2694 . 
       FIGS. 26O and 26P  shows a partial sectional view and a perspective view of an embodiment of a cinching mechanism comprising a punched disk. Cinching mechanism  2602 ′ comprises a disk  2604 ′ comprising a punched hole  2606 ′. Punched hole  2606 ′ is made by punching disk  2604 ′ along the proximal direction such that the punching action leaves an edge that is biased along the proximal direction as shown in  FIG. 26O . Disk  2604 ′ can slide over a tension element  2608 ′ along the distal direction. However, motion of disk  2604 ′ over tension element  2608 ′ along the proximal direction is substantially resisted by the proximally biased edges of punched hole  2606 ′. 
     Excess lengths of tension elements or other severable regions of one or more devices disclosed in this patent application may be cut, severed or trimmed using one or more cutting devices. For example,  FIGS. 26Q and 26R  show a perspective view of a first embodiment of a cutting device before and after cutting an elongate element. In  FIG. 26Q , cutting device  2610 ′ comprises an outer sheath  2612 ′ comprising a sharp distal edge  2614 ′. Outer sheath  2612 ′ encloses an inner sheath  2616 ′. Inner diameter of outer sheath  2612 ′ is slightly larger than outer diameter of inner sheath  2616 ′ such that inner sheath  2616 ′ can slide easily through outer sheath  2612 ′. Inner sheath  2616 ′ comprises a lumen that terminates distally in an opening  2618 ′. An elongate severable device passes through the lumen and emerges out of opening  2618 ′. An example of an elongate severable device is a tension element  2620 ′. In the method of cutting or trimming tension element  2620 ′ the desired area of tension element  2620 ′ to be cut or severed is positioned near opening  2618 ′ by advancing or withdrawing cutting device  2610 ′ over tension element  2620 ′. Thereafter, outer sheath  2612 ′ is advanced over inner sheath  2616 ′ to cut tension element  2620 ′ between sharp distal edge  2614 ′ and an edge of opening  2618 ′. Inner sheath  2616 ′ and outer sheath  2612 ′ may be substantially rigid or flexible. They may be made of suitable materials including, but not limited to Pebax, Polyimide, Braided Polyimide, Polyurethane, Nylon, PVC, Hytrel, HDPE, PEEK, metals like stainless steel and fluoropolymers like PTFE, PFA, FEP and EPTFE etc. 
       FIG. 26S  show a crossectional view of a second embodiment of a cutting device for cutting an elongate element. Cutting device  2622 ′ comprises an outer sheath  2624 ′ comprising a lumen that opens in an opening  2626 ′ in outer sheath  2624 ′. Outer sheath  2624 ′ encloses an inner sheath  2628 ′ that comprises a lumen and a sharp distal edge  2630 ′. Inner diameter of outer sheath  2624 ′ is slightly larger than outer diameter of inner sheath  2628 ′ such that inner sheath  2628 ′ can slide easily through outer sheath  2624 ′. An elongate severable device passes through the lumen of inner sheath  2628 ′ and emerges out of distal end of inner sheath  2628 ′ and out of outer sheath  2624 ′ through opening  2626 ′. An example of an elongate severable device is a tension element  2632 ′. In the method of cutting or trimming tension element  2632 ′ the desired area of tension element  2632 ′ to be cut or severed is positioned near opening  2626 ′ by advancing or withdrawing cutting device  2622 ′ over tension element  2632 ′. Thereafter, inner sheath  2628 ′ is advanced through outer sheath  2624 ′ to cut tension element  2632 ′ between sharp distal edge  2630 ′ and an edge of opening  2626 ′. Inner sheath  2628 ′ and outer sheath  2624  may be substantially rigid or flexible. They may be made of suitable materials including, but not limited to Pebax, Polyimide, Braided Polyimide, Polyurethane, Nylon, PVC, Hytrel, HDPE, PEEK, metals like stainless steel and fluoropolymers like PTFE, PFA, FEP and EPTFE etc. 
     In a third embodiment of a cutting device for cutting an elongate element, the cutting device comprises an outer hollow sheath. Outer hollow sheath has a distal end plate comprising a window. An elongate severable device passes through the window. An example of an elongate severable device is a tension element. An inner shaft can slide and rotate within outer hollow sheath. Distal end of inner shaft comprises a blade that is usually located away from the window and adjacent to the distal end plate of the outer hollow sheath. In the method of cutting or trimming tension element the elongate severable device, the desired area of the elongate severable device to be cut or severed is positioned near the window. This is done by advancing or withdrawing the cutting device over the elongate severable device. Thereafter, the inner shaft is rotated within outer hollow sheath such that the blade cuts the elongate severable device between a sharp edge of the blade and an edge of the window. Inner shaft and outer hollow sheath may be substantially rigid or flexible. They may be made of suitable materials including, but not limited to Pebax, Polyimide, Braided Polyimide, Polyurethane, Nylon, PVC, Hytrel, HDPE, PEEK, metals like stainless steel and fluoropolymers like PTFE, PFA, FEP and EPTFE etc. The end plate and the blade are preferentially rigid. They may be made of suitable materials including, but not limited to metals like stainless steel, polymers like Polycarbonate, Polyimide, PVC, Hytrel, HDPE, PEEK and fluoropolymers like PTFE, PFA, FEP etc. 
     The anchoring devices disclosed herein may be used in a variety of configurations depending on the location of the disease process, ease of procedure etc.  FIGS. 27A through 27D  show axial sections through the prostate gland PG showing various configurations of anchoring devices comprising distal anchors  2700  and a tension element  2702  that is anchored at a suitable location such that a sufficient tension exists in tension element  2702 . 
       FIGS. 28 and 28A  show perspective views of an embodiment of an anchoring device comprising an elongate element comprising multiple barbs or anchors.  FIG. 28  shows a perspective view of anchoring device  2800  comprising an elongate element  2802 . Elongate element  2802  can be made of several biocompatible materials including, but not limited to synthetic fibers e.g. various grades of Nylon, polyethylene, polypropylene, polyester, Aramid etc.; metals e.g. various grades of stainless steel, titanium, nickel-titanium alloys, cobalt-chromium alloys, tantalum etc.; natural fibers e.g. cotton, silk etc.; rubber materials e.g. various grades of silicone rubber etc. Elongate element  2802  may comprise natural or artificial suture materials. Examples of such materials include but are not limited to Polyamide (Nylon), Polypropylene, Polyglycolic Acid (PGA), polylactic acid (PLA) and copolymers of polylactic acid, polyglycolic acid and copolymers of polyglycolic acid, copolymers of PLA and PGA, Silk, Polyester, silicone, collagen, Polymers of Glycolide and Lactide. A particular example of a suture is the Nordstrom suture which is a highly elastic silicone suture. In one embodiment, the suture material is bioabsorbable. Elongate element  2802  comprises two sets of projections such as barbs, anchors or hooks. In the example shown, elongate element  2802  comprises a set of distal barbs  2804  and a set of proximal barbs  2806 . Distal barbs  2804  are oriented in the proximal direction and proximal barbs  2806  are oriented in the distal direction as shown in  FIG. 25 .  FIG. 28A  shows a magnified view of the region  28 A of anchoring device  2800  showing proximal barbs  2806 . 
       FIGS. 28B through 28E  show a coronal section through the prostate gland PG showing various steps of a method of treating the prostate gland PG using the device of  FIG. 28 . In  FIG. 28B , introducer device  300  of  FIG. 3A  comprising a working device lumen and a cystoscope lumen  308  is introduced into the urethra such that the distal end of introducer device  300  is located in the prostatic urethra. Thereafter, a hollow puncturing device  2808  is inserted in the working device lumen of introducer device. Puncturing device  2808  is advanced such that distal end of puncturing device  2808  penetrates the prostate gland PG. In  FIG. 28C , anchoring device  2800  is introduced through puncturing device  2808  into the prostate gland PG. Thereafter, puncturing device  2808  is pulled in the proximal direction. Simultaneously, anchoring device  2800  is pulled in the proximal direction to anchor distal barbs  2804  in the anatomy. In  FIG. 28D , puncturing device  2808  is pulled further in the proximal direction to expose the entire anchoring device  2800 . Thereafter, in step  28 E, the proximal end of anchoring device  2800  is detached to deploy anchoring device  2800  in the anatomy. Thus, tissue between distal barbs  2804  and proximal barbs  2806  is anchored to anchoring device  2800 . 
       FIG. 29A  shows an axial section of the prostate gland PG showing a pair of implanted magnetic anchors. In  FIG. 29A , a first magnetic anchor  2900  and a second magnetic anchor  2902  are implanted in the prostate gland PG on either side of the urethra. Like poles of first magnetic anchor  2900  and second magnetic anchor  2902  face each other such that there is magnetic repulsion between first magnetic anchor  2900  and second magnetic anchor  2902 . This causes the urethral lumen to widen potentially reducing the severity of BPH symptoms. 
       FIGS. 29B through 29D  show a coronal section through the prostate gland PG showing the steps of a method of implanting magnetic anchors of  FIG. 29A . In  FIG. 29B , a deployment device  2904  is advanced transurethrally. Deployment device  2904  comprises a sharp distal tip  2906  and first magnetic anchor  2900 . Distal tip  2906  of deployment device  2904  penetrates prostatic tissue and implants first magnetic anchor  2900  in the prostate gland PG. Similarly, another deployment device  2908  comprising a sharp distal tip  2920  is used to implant second magnetic anchor  2902  in the prostate gland PG. First magnetic anchor  2900  and second magnetic anchor  2902  are implanted on opposite sides of the urethra such that like poles of first magnetic anchor  2900  and second magnetic anchor  2902  face each other. This causes magnetic repulsion between first magnetic anchor  2900  and second magnetic anchor  2902 . This causes the urethral lumen to widen potentially reducing the severity of BPH symptoms. In one embodiment, deployment device  2904  can be used to deploy multiple magnetic anchors. 
       FIG. 30A  shows a coronal section of a region of the male urinary system showing the general working environment of a method of treating prostate disorders by cutting prostrate tissue using a device inserted into the prostate gland PG from the urethra. Cutting device  3000  comprises an outer body  3002  comprising a side port  3004 . Outer body  3002  can be made of suitable biocompatible materials including, but not limited to metals e.g. stainless steel, Nickel-Titanium alloys, titanium etc.; polymers e.g. etc. Cutting device  3000  further comprises an access device  3006  that can be deployed out of side port  3004 . Access device  3006  can be retracted back into side port  3004 . Typical examples of elements that can be used as access device  3006  are needles, trocars etc. Access device  3006  may be made from suitable biocompatible materials including, but not limited to metals e.g. stainless steel, Nickel-Titanium alloys, titanium etc.; polymers e.g. etc. Access device  3006  penetrates the walls of the urethra and enters the prostate gland PG by creating an access channel in the prostate gland PG. Cutting device  3000  further comprises a cutting element  3008  that is introduced into the prostate gland PG through the access channel in the prostate gland PG. In one embodiment, cutting element  3008  enters the prostate gland PG through access device  3006 . Cutting element  3008  comprises one or more cutting modalities such as electrosurgical cutter, Laser cutter, mechanical cutter e.g. a knife edge etc. Cutting element  3008  may be moved through prostate tissue by several mechanisms including one or more deflecting or bending elements located on cutting element  3008 ; one or more articulating elements located on cutting element  3008 ; motion of cutting device  3000  along the urethra etc. Cutting element  3008  is used to cut one or more regions of the prostate gland PG including peripheral zone, transition zone, central zone or prostatic capsule. After the desired region or regions of the prostate gland PG are cut, cutting element  3008  and access device  3006  are withdrawn into cutting device  3000 . Thereafter, cutting device  3000  is withdrawn from the urethra. In one device embodiment, cutting device  3000  comprises an endoscope or means for inserting an endoscope. 
       FIG. 30B  shows a coronal section of a region of the male urinary system showing the general working environment of a method of treating prostate disorders by cutting prostrate tissue using a device that accesses outer surface of the prostate gland PG by passing through the walls of the urethra distal to the prostate gland PG. Cutting device  3020  comprises an outer body  3022  comprising a side port  3024 . Outer body  3022  can be made of suitable biocompatible materials including, but not limited to metals e.g. stainless steel, Nickel-Titanium alloys, titanium etc.; polymers e.g. etc. Cutting device  3020  is advanced into the urethra such that side port  3024  is located distal to the prostate gland PG. Cutting device  3020  further comprises an access device  3026  that can be deployed out of side port  3024 . Access device  3026  can be retracted back into side port  3024 . Typical examples of elements that can be used as access device  3026  are needles, trocars etc. Access device  3026  may be made from suitable biocompatible materials including, but not limited to metals e.g. stainless steel, Nickel-Titanium alloys, titanium etc.; polymers e.g. etc. Access device  3026  is deployed from side port  3024  in a desired orientation such that access device  3026  penetrates the wall of the urethra. Access device  3026  is advanced further such that distal end of access device  3026  is located near the prostate gland PG. Thereafter, a cutting element  3028  is introduced through access device  3026  to the outer surface of the prostate gland PG. Cutting element  3028  comprises one or more cutting modalities such as electrosurgical cutter, Laser cutter, mechanical cutter e.g. a knife edge etc. Cutting element  3028  is used to cut one or more regions of the prostate gland PG including prostatic capsule, peripheral zone, transition zone or central zone. Cutting element  3028  may be moved relative to prostate tissue by several mechanisms including one or more deflecting or bending elements located on cutting element  3028 ; motion of cutting element  3028  along access device  3026  etc. In one method embodiment, cutting element  3028  cuts prostatic capsule while being withdrawn into access device  3026 . After the desired region or regions of the prostate gland PG are cut, cutting element  3028  and access device  3026  are withdrawn into cutting device  3020 . Thereafter, cutting device  3020  is withdrawn from the urethra. In one device embodiment, cutting device  3020  further comprises an endoscope or means for inserting an endoscope. 
       FIG. 30C  shows a coronal section of a region of the male urinary system showing the general working environment of a method of treating prostate disorders by cutting prostrate tissue using a device that accesses outer surface of the prostate gland PG by passing through the wall of the urinary bladder. Cutting device  3040  comprises an outer body  3042  comprising a side port  3044 . Outer body  3042  can be made of suitable biocompatible materials including, but not limited to metals e.g. stainless steel, Nickel-Titanium alloys, titanium etc.; polymers e.g. etc. Cutting device  3040  is advanced into the urethra such that side port  3044  is located inside the urinary bladder. Cutting device  3040  further comprises an access device  3046  that can be deployed out of side port  3044 . Access device  3046  can be retracted back into side port  3044 . Typical examples of elements that can be used as access device  3046  are needles, trocars etc. Access device  3046  may be made from suitable biocompatible materials including, but not limited to metals e.g. stainless steel, Nickel-Titanium alloys, titanium etc.; polymers e.g. etc. Access device  3046  is deployed from side port  3044  in a desired orientation such that access device  3046  penetrates the wall of the urinary bladder. Access device  3046  is advanced further such that distal end of access device  3046  is located near the prostate gland PG. Thereafter, a cutting element  3048  is introduced through access device  3046  to the outer surface of the prostate gland PG. Cutting element  3048  comprises one or more cutting modalities such as electrosurgical cutter, Laser cutter, mechanical cutter e.g. a knife edge etc. Cutting element  3048  is used to cut one or more regions of the prostate gland PG including prostatic capsule, peripheral zone, transition zone or central zone. Cutting element  3048  may be moved relative to prostate tissue by several mechanisms including one or more deflecting or bending elements located on cutting element  3048 ; motion of cutting element  3048  along access device  3046  etc. In one method embodiment, cutting element  3048  cuts prostatic capsule while being withdrawn into access device  3046 . After the desired region or regions of the prostate gland PG are cut, cutting element  3048  and access device  3046  are withdrawn into cutting device  3040 . Thereafter, cutting device  3040  is withdrawn from the urethra. In one device embodiment, cutting device  3040  further comprises an endoscope or means for inserting an endoscope. 
       FIG. 30D  shows a coronal section of a region of the male urinary system showing the general working environment of a method of treating prostate disorders by cutting prostrate tissue using a device that accesses outer surface of the prostate gland PG by passing through the walls of the urethra enclosed to the prostate gland PG. Cutting device  3060  comprises an outer body  3062  comprising a side port  3064 . Outer body  3062  can be made of suitable biocompatible materials including, but not limited to metals e.g. stainless steel, Nickel-Titanium alloys, titanium etc.; polymers e.g. etc. Cutting device  3060  is advanced into the urethra such that side port  3064  is located in the region of the urethra enclosed by the prostate gland PG. Cutting device  3060  further comprises an access device  3066  that can be deployed out of side port  3064 . Access device  3066  can be retracted back into side port  3064 . Typical examples of elements that can be used as access device  3066  are needles, trocars etc. Access device  3066  may be made from suitable biocompatible materials including, but not limited to metals e.g. stainless steel, Nickel-Titanium alloys, titanium etc.; polymers e.g. etc. Access device  3066  is deployed from side port  3064  in a desired orientation such that access device  3066  penetrates the prostate. Thereafter, a cutting element  3068  is introduced through access device  3066  such that the distal region of cutting element can access the outer surface of the prostate gland PG. Cutting element  3068  comprises one or more cutting modalities such as electrosurgical cutter, Laser cutter, mechanical cutter e.g. a knife edge etc. Cutting element  3068  is used to cut one or more regions of the prostate gland PG including prostatic capsule, peripheral zone, transition zone or central zone. Cutting element  3068  may be moved relative to prostate tissue by several mechanisms including one or more deflecting or bending elements located on cutting element  3068 ; motion of cutting element  3068  along access device  3066  etc. In one method embodiment, cutting element  3068  cuts prostatic capsule while being withdrawn into access device  3066 . After the desired region or regions of the prostate gland PG are cut, cutting element  3068  and access device  3066  are withdrawn into cutting device  3060 . Thereafter, cutting device  3060  is withdrawn from the urethra. In one device embodiment, cutting device  3060  further comprises an endoscope or means for inserting an endoscope. 
       FIG. 31  shows a coronal section of a region of the male urinary system showing the general working environment of a method of treating prostate disorders by cutting prostrate tissue by a percutaneous device that accesses the prostate gland PG through an incision in the abdomen. In this method, a cannula  3100  is introduced percutaneously into the lower abdomen. Cannula  3100  can be made of suitable biocompatible materials including, but not limited to metals e.g. stainless steel, Nickel-Titanium alloys, titanium etc.; polymers etc. Cannula  3100  is advanced into the abdomen such that it passes below the pubic bone. The distal end of cannula  3100  is positioned near the prostate gland PG. Thereafter, a cutting device  3102  is advanced through distal end of cannula  3100  to the outer surface of the prostate gland PG. Cutting device  3102  can be retracted back into cannula  3100 . Cutting device  3102  comprises one or more cutting modalities such as electrosurgical cutter, Laser cutter, mechanical cutter e.g. a knife edge etc. Cutting device  3102  is used to cut one or more regions of the prostate gland PG including prostatic capsule, peripheral zone, transition zone or central zone. Cutting device  3102  may be moved relative to prostate tissue by several mechanisms including one or more deflecting or bending elements located on cutting device  3102 ; motion of cutting device  3102  along cannula  3100  etc. In one method embodiment, cutting device  3102  cuts prostatic capsule while being withdrawn into cannula  3100 . After the desired region or regions of the prostate gland PG are cut, cutting device  3102  is withdrawn into cannula  3100 . Thereafter, cannula  3100  is withdrawn from the urethra. In one device embodiment, cannula  3100  further comprises an endoscope or means for inserting an endoscope. 
       FIG. 32  shows a coronal section of a region of the male urinary system showing the general working environment of a method of treating prostate disorders by cutting prostrate tissue by a percutaneous device that penetrates the urinary bladder and accesses the outer surface of the prostate gland PG through an incision in the urinary bladder. In this method, a cannula  3200  is introduced percutaneously into the lower abdomen. Cannula  3200  can be made of suitable biocompatible materials including, but not limited to metals e.g. stainless steel, Nickel-Titanium alloys, titanium etc.; polymers etc. Cannula  3200  is advanced into the abdomen such that it passes above the pubic bone. The distal end of cannula  3200  enters the urinary bladder. Thereafter, an access device  3202  is advanced through cannula  3200  such that access device  3202  penetrates the urinary bladder wall as shown in  FIG. 4 . Thereafter, a cutting device  3204  is advanced through distal end of access device  3202  to the outer surface of the prostate gland PG. Cutting device  3202  can be retracted back into access device  3202 . Cutting device  3202  comprises one or more cutting modalities such as electrosurgical cutter, Laser cutter, mechanical cutter e.g. a knife edge etc. Cutting device  3202  is used to cut one or more regions of the prostate gland PG including prostatic capsule, peripheral zone, transition zone or central zone. Cutting device  3202  may be moved relative to prostate tissue by several mechanisms including one or more deflecting or bending elements located on cutting device  3202  or access device  3202 ; motion of cutting device  3202  along access device  3202  etc. In one method embodiment, cutting device  3202  cuts prostatic capsule while being withdrawn into access device  3202 . After the desired region or regions of the prostate gland PG are cut, cutting device  3202  is withdrawn into access device  3202 . Access device  3202  is then withdrawn into cannula  3200 . Thereafter, cannula  3200  is withdrawn from the urinary bladder. In one device embodiment, cannula  3200  further comprises an endoscope or means for inserting an endoscope. 
       FIG. 33  series shows a perspective view of a prostate treatment kit to cut prostate tissue.  FIG. 33A  shows a perspective view of an introducer device. Introducer device  3300  comprises a first tubular element  3302  enclosing a working device lumen  3304 . First tubular element  3302  can be made of suitable biocompatible materials such as Pebax, Polyimide, Braided Polyimide, Polyurethane, Nylon, PVC, Hytrel, HDPE, PEEK, metals like stainless steel and fluoropolymers like PTFE, PFA, FEP and EPTFE etc. The proximal end of working device lumen  3304  comprises a first stasis valve  3306 . The distal end of working device lumen  3304  comprises a deflection mechanism. The deflection mechanism is used to bend the distal region of working device lumen  3304 . One example of deflection mechanism is a pull wire and a deflection dial  3310  to adjust the magnitude and/or the direction of deflection caused by the pull wire. Similarly, other deflection mechanisms can be used in the introducer device instead of a pull wire. Introducer device  3300  further comprises a second tubular element  3312  which encloses a cystoscope lumen  3314 . A cystoscope can be introduced through cystoscope lumen  3314  into the urethra. Typical examples of cystoscopes that can be used with introducer device are those manufactured by Olympus, Pentax, Storz, Wolf, Circon-ACMI, etc. These may have pre-set angles (i.e. 0, 30, 70, 120 degrees) or may be flexible scopes where in the tip may be deflectable. The proximal end of cystoscope lumen  3314  comprises a second stasis valve  3316 . The cystoscope is inserted through the proximal end of cystoscope lumen  3314  and emerges out into the urethra from the distal end of cystoscope lumen  3314 . The cystoscope can then be used to visualize the anatomy and various instruments during a procedure. Working device lumen  3314  may comprise one or more side ports e.g. a first side port  3318  for the introduction or removal of one or more fluids. Cystoscope lumen  3314  may comprise one or more side ports e.g. a second side port  3320  for the introduction or removal of one or more fluids. 
       FIG. 33B  shows a perspective view of an injecting needle. Injecting needle  3330  is used for injecting one or more diagnostic or therapeutic agents in the anatomy. In one method embodiment, injecting needle  3330  is used to inject local anesthetic in the urethra and/or prostate gland PG. Specific examples of target areas for injecting local anesthetics are the neurovascular bundles, the genitourinary diaphragm, the region between the rectal wall and prostate, etc. Examples of local anesthetics that can be injected by injecting needle  3330  are anesthetic solutions e.g. 1% lidocaine solution; anesthetic gels e.g. lidocaine gels; combination of anesthetic agents e.g. combination of lidocaine and bupivacaine; etc. Injecting needle  3330  comprises a hollow shaft  3332  made of suitable biocompatible materials including, but not limited to stainless steel 304, stainless steel 306, Nickel-Titanium alloys, titanium etc. The length of hollow shaft  3332  can range from to centimeters. The distal end of hollow shaft  3332  comprises a sharp tip  3334 . The proximal end of hollow shaft  3332  has a needle hub  3336  made of suitable biocompatible materials including, but not limited to metals e.g. like stainless steel 304, stainless steel 306, Nickel-Titanium alloys, titanium etc.; polymers e.g. polypropylene etc. In one embodiment, needle hub  3336  comprises a luer lock. 
       FIG. 33C  shows a perspective view of a guiding device. Guiding device  3338  comprises an elongate body  3340  comprising a sharp distal tip  3342 . In one embodiment, guiding device  3338  is a guidewire. Distal end of elongate body  3340  may comprise an anchoring element to reversibly anchor guiding device  3338  into tissue. Examples of suitable anchoring elements are barbs, multipronged arrowheads, balloons, other mechanically actuable members (e.g. bendable struts), screw tips, shape memory elements, or other suitable anchor designs disclosed elsewhere in this patent application. 
       FIG. 33D  shows a perspective view of a RF cutting device. Cutting device  3343  comprises an inner sheath  3344  and an outer sheath  3346 . Inner sheath  3344  comprises a lumen of a suitable dimension such that cutting device  3343  can be advanced over guiding device  538 . Outer sheath  3346  can slide on inner sheath  3344 . Outer sheath  3346  also comprises two marker bands: a proximal marker band  3348  and a distal marker band  3350 . The marker bands can be seen by a cystoscope. In one embodiment, proximal marker band  3348  and distal marker band  3350  are radiopaque. The position of proximal marker band  3348  and distal marker band  3350  is such that after cutting device  3343  is placed in an optimum location in the anatomy, proximal marker band  3348  is located in the urethra where it can be seen by a cystoscope and distal marker band  3350  is located in the prostrate gland PG or in the wall of the urethra where it cannot be seen by the cystoscope. Cutting device  3343  further comprises a cutting wire  3352  that is capable of delivering electrical energy to the surrounding tissue. The distal end of cutting wire  3352  is fixed to the distal region of outer sheath  3344 . The proximal end of cutting wire  3352  is connected to a distal region of outer sheath  3346  and is further connected to a source of electrical energy. In  FIG. 33D , cutting wire  3352  is in an undeployed configuration. FIG.  33 D′ shows the distal region of cutting device  3343  when cutting wire  3352  is in a deployed configuration. To deploy cutting wire  3352 , inner sheath  3344  is moved in the proximal direction with respect to outer sheath  546 . This causes cutting wire  3352  to bend axially outward thus deploying cutting wire  3352  in the surrounding anatomy. 
       FIG. 33E  shows a perspective view of an embodiment of a plugging device to plug an opening created during a procedure. Plugging device  3354  comprises a tubular shaft  3356  comprising a distal opening  3358 . Distal opening  3358  is used to deliver one or more plugging materials  3360  in the adjacent anatomy. Plugging material  3360  may comprise a porous or non-porous matrix formed of a biodegradable or non-biodegradable material such as a flexible or rigid polymer foam, cotton wadding, gauze, hydrogels, etc. Examples of biodegradable polymers that may be foamed or otherwise rendered porous include but are not restricted to polyglycolide, poly-L-lactide, poly-D-lactide, poly(amino acids), polydioxanone, polycaprolactone, polygluconate, polylactic acid-polyethylene oxide copolymers, modified cellulose, collagen, polyorthoesters, polyhydroxybutyrate, polyanhydride, polyphosphoester, poly(alpha-hydroxy acid) and combinations thereof. In one embodiment, plugging material  3360  comprises biocompatible sealants including but not limited to fibrin sealants, combination of natural proteins (e.g. collagen, albumin etc.) with aldehyde cross-linking agents (e.g. glutaraldehyde, formaldehyde) or other polymeric, biological or non-polymeric materials capable of being implanted with the body, etc. Plugging device  3354  may be introduced in the anatomy by various approaches including the approaches disclosed elsewhere in this patent application. Plugging device  3354  may be introduced in the anatomy through a cannula, over a guiding device such as a guidewire etc. In the embodiment shown in  FIG. 33E , plugging material  3360  is preloaded in plugging device  3354 . Plugging material  3360  is introduced through distal opening  3358  by pushing plunger  3362  in the distal direction. In another embodiment, plugging device  3354  comprises a lumen that extends from the proximal end to distal opening  3358 . Plugging material  3360  may be injected through the proximal end of the lumen such that it emerges out through distal opening  3358 . 
       FIGS. 33F through 33N  show various alternate embodiments of the electrosurgical cutting device in  FIG. 33D .  FIGS. 33F and 33G  show perspective views of the distal region of a first alternate embodiment of an electrosurgical cutting device in the undeployed and deployed states respectively.  FIG. 33F  show an electrosurgical cutting device  570  comprising an elongate shaft  3372 . Shaft  3372  is made of an electrically insulating material. Electrosurgical cutting device  3370  further comprises an electrosurgical cutting wire  3374 . Electrosurgical cutting wire  3374  can be made of a variety of materials including, but not limited to tungsten, stainless steel, etc. Distal end of cutting wire  3374  is attached to distal region of shaft  3372 . The proximal region of cutting wire  3374  can be pulled in the proximal direction by an operator. In one embodiment, electrosurgical cutting device  3370  is introduced in the target anatomy through a sheath  3376 . In  FIG. 33F , electrosurgical cutting device  3370  is deployed by pulling cutting wire  3374  in the proximal direction. This causes distal region of shaft  3372  to bend. Thereafter, electrical energy is delivered through cutting wire  3374  to cut tissue. This may be accompanied by motion of electrosurgical cutting device  3370  along the proximal or distal direction. 
       FIGS. 33H and 33I  show perspective views of the distal region of a second alternate embodiment of an electrosurgical cutting device in the undeployed and deployed states respectively. Electrosurgical cutting device  3380  comprises an elongate sheath  3382  comprising a lumen. Distal region of sheath  3382  has a window  3384 . Electrosurgical cutting device  3380  further comprises an electrosurgical cutting wire  3386  located in the lumen. Distal end of cutting wire  3386  is fixed to the distal end of sheath  3384 . Proximal end of cutting wire  3386  can be pushed in the distal direction by a user. In  FIG. 33I , cutting wire  3386  is deployed by pushing cutting wire  3386  in the distal direction. This causes a region of cutting wire  3386  to bend in the radially outward direction and thus emerge out of window  3384 . Thereafter, electrical energy is delivered through cutting wire  3386  to cut tissue. This may be accompanied by motion of electrosurgical cutting device  3380  along the proximal or distal direction. 
       FIGS. 33J through 33L  show perspective views of the distal region of a second alternate embodiment of an electrosurgical cutting device showing the steps of deploying the electrosurgical cutting device. Electrosurgical cutting device  3390  comprises an elongate sheath  3391  comprising a lumen  3392 . In  FIG. 33J , an electrosurgical cutting wire  3394  is introduced through lumen  3392  such that it emerges out through the distal opening of lumen  3392 . In  FIG. 33K , cutting wire  3394  is further advanced in the distal direction. Distal end of cutting wire  3394  has a curved region so that cutting wire  3394  starts to bend as it emerges out of lumen  3392 . IN  FIG. 33L , cutting wire  3394  is further advanced in the distal direction to fully deploy cutting wire  3394 . Thereafter, electrical energy is delivered through cutting wire  3394  to cut tissue. This may be accompanied by motion of electrosurgical cutting device  3390  along the proximal or distal direction. 
       FIGS. 33M through 33N  show perspective views of the distal region of a third alternate embodiment of an electrosurgical cutting device showing the steps of deploying the electrosurgical cutting device. Electrosurgical cutting device  3395  comprises an elongate sheath  3396  comprising a lumen. Cutting device  3395  further comprises a cutting wire  3398  located in the lumen of elongate sheath  3396 . The proximal end of cutting wire  3398  is connected to a source of electrical energy. Distal end of cutting wire  3398  is connected to the inner surface of the distal region of elongate sheath  3396 . Cutting wire  3398  may be made from suitable elastic, super-elastic or shape memory materials including but not limited to Nitinol, titanium, stainless steel etc. In  FIG. 33N , Electrosurgical cutting device  3395  is deployed by pushing the proximal region of cutting wire  3398  in the distal direction. This causes a distal region of cutting wire  3398  to emerge from the distal end of elongate sheath  3396  as a loop. Thereafter, electrical energy is delivered through cutting wire  3398  to cut tissue. This may be accompanied by motion of electrosurgical cutting device  3395  along the proximal or distal direction. Electrosurgical cutting device  3395  can be used to cut multiple planes of tissue by withdrawing cutting wire  3398  in elongate sheath  3396 , rotating elongate sheath  3396  to a new orientation, redeploying cutting wire  3398  and delivering electrical energy through cutting wire  3398 . The devices  33 H through  33 N may be introduced by one or more access devices such as guidewires, sheaths etc. 
       FIG. 34  shows a perspective view of the distal region of a balloon catheter comprising a balloon with cutting blades. Balloon catheter  3400  can be introduced into a lumen or in the tissue of an organ to be treated using one or more of the introducing methods disclosed elsewhere in this patent application. Balloon catheter  3400  comprises a shaft  3402 . Shaft  3402  may comprise a lumen to allow balloon catheter  3400  to be introduced over a guidewire. In one embodiment, shaft  3402  is torquable. Shaft  3402  comprises a balloon  3404  located on the distal end of shaft  3402 . Balloon  3404  can be fabricated from materials including, but not limited to polyethylene terephthalate, Nylon, polyurethane, polyvinyl chloride, crosslinked polyethylene, polyolefins, HPTFE, HPE, HDPE, LDPE, EPTFE, block copolymers, latex and silicone. Balloon  3404  further comprises one or more cutter blades  3406 . Balloon catheter  3400  is advanced with balloon  3404  deflated, into a natural or surgically created passageway and positioned adjacent to tissue or matter that is to be cut, dilated, or expanded. Thereafter, balloon  3404  is inflated to cause cutter blades  3406  to make one or more cuts in the adjacent tissue or matter. Thereafter balloon  3404  is deflated and balloon catheter  3400  is removed. Cutter blades  3406  may be energized with mono or bi-polar RF energy. Balloon catheter  3400  may comprise one or more navigation markers including, but not limited to radio-opaque markers, ultrasound markers, light source that can be detected visually etc. 
       FIG. 35  shows a perspective view of the distal region of a balloon catheter comprising a balloon with cutting wires. Balloon catheter  3500  can be introduced into a lumen or in the tissue of an organ to be treated using one or more of the introducing methods disclosed elsewhere in this patent application. Balloon catheter  3500  comprises a shaft  3502 . Shaft  3502  may comprise a lumen to allow balloon catheter  3500  to be introduced over a guidewire. In one embodiment, shaft  3502  is torquable. Shaft  3502  comprises a balloon  3504  located on the distal end of shaft  3502 . Balloon  3504  can be fabricated from materials including, but not limited to polyethylene terephthalate, Nylon, polyurethane, polyvinyl chloride, crosslinked polyethylene, polyolefins, HPTFE, HPE, HDPE, LDPE, EPTFE, block copolymers, latex and silicone. Balloon  3504  further comprises one or more radiofrequency wires  3506 . Balloon catheter  3500  is advanced with balloon  3504  deflated, into a natural or surgically created passageway and positioned adjacent to tissue or matter that is to be cut, dilated, or expanded. Thereafter, balloon  3504  is inflated and an electrical current is delivered through radiofrequency wires  3506  to make one or more cuts in the adjacent tissue or matter. Thereafter the electrical current is stopped, balloon  3504  is deflated and balloon catheter  3500  is removed. Radiofrequency wires  3504  may be energized with mono or bi-polar RF energy. Balloon catheter  3500  may comprise one or more navigation markers including, but not limited to radio-opaque markers, ultrasound markers, light source that can be detected visually etc. 
       FIGS. 36A and 36B  series show perspective views of an undeployed state and a deployed state respectively of a tissue displacement device.  FIG. 36A  shows a tissue anchoring device  3600  in the undeployed state. Anchoring device  3600  comprises an elongate body having a proximal end  3602  and a distal end  3604 . Anchoring device  3600  may be made of a variety of elastic or super-elastic materials including, but not limited to Nitinol, stainless steel, titanium etc. Anchoring device  3600  is substantially straight in the undeployed state and has a tendency to become substantially curved in the deployed state. Anchoring device  3600  is maintained in the undeployed state by a variety of means including, but not limited to enclosing anchoring device  3600  in a cannula or sheath, etc.  FIG. 36B  shows tissue anchoring device  3600  in the deployed state. Anchoring device  3600  comprises a curved region. When anchoring device  3600  changes from an undeployed state to a deployed state, the anatomical tissue adjacent to the central region of anchoring device  3600  is displaced along the direction of motion of the central region. Anchoring device  3600  can be deployed by a variety of methods including, but not limited to removing anchoring device  3600  from a sheath or cannula, etc. In one embodiment, anchoring device  3600  is made from a shape memory material such as Nitinol. In this embodiment, anchoring device  3600  is maintained in the undeployed state by maintaining anchor device  3600  in a temperature lower than the transition temperature of the super-elastic material. Anchoring device  3600  is converted to the deployed state by implanting anchoring device  3600  in a patient such that the device is warmed to the body temperature which is above the transition temperature of the super-elastic material. 
       FIGS. 36C and 36D  show a coronal view and a lateral view respectively of a pair of deployed tissue displacement devices of  FIGS. 36A and 36B  implanted in the prostate gland PG. In  FIG. 36C , two anchoring devices are implanted in the prostate gland PG near the prostatic urethra in a patient with BPH. A first anchoring device  3600  is introduced on a first side of the urethra and is deployed there as shown. Similarly, a second anchoring device  3606  comprising a proximal end  3608  and a distal end  3610  is introduced on the other side of the urethra and is deployed there as shown. First anchoring device  3600  and second anchoring device  3606  change into the deployed curved configuration. This causes prostate gland PG tissue near the central regions of first anchoring device  3600  and second anchoring device  3606  to be displaced radially away from the urethra. This displacement of prostate gland PG tissue can be used to eliminate or reduce the compression of the urethra by an enlarged prostate gland PG.  FIG. 36D  shows a lateral view of the urethra enclosed by the prostate gland PG showing deployed first anchoring device  3600  and second anchoring device  3606 . 
     The various cuts or punctures made by one or more cutting devices disclosed in this patent application may be plugged or lined by a plugging or space filling substance.  FIGS. 36E through 36H  show an axial section through a prostate gland showing the various steps of a method of cutting or puncturing the prostate gland and lining or plugging the cut or puncture.  FIG. 36E  shows a section of the prostate gland showing the urethra, the lateral lobes and the middle lobe surrounded by the prostatic pseudocapsule. In  FIG. 36F , one or more cuts are made in a region of the prostatic pseudocapsule. In addition, one or more cuts may be made in a region of between two lobes of the prostate gland. In  FIG. 36G , a plugging material  3619  is introduced in the one or more regions of the prostate gland that are cut or punctured. Plugging material  3619  may be delivered through one or more delivery devices including, but not limited to the device disclosed in  FIG. 33E . Plugging material  3619  may comprises a material such as plugging material  3360 . 
     The various cuts or punctures made by one or more cutting devices disclosed in this patent application may be spread open by a clipping device. For example,  FIG. 36H  shows an axial section through a prostate gland showing a clip for spreading open a cut or punctured region of the prostate gland. Spreading device  3620  comprises a body having a central region and two distal arms. Spreading device  3620  may be made of a variety of elastic or super-elastic materials including, but not limited to Nitinol, stainless steel, titanium etc. Spreading device  3620  has a reduced profile in the undeployed state by maintaining distal arms close to each other. Spreading device  5000  is maintained in the undeployed state by a variety of means including, but not limited to enclosing spreading device  3620  in a cannula or sheath, etc. When spreading device  3620  changes from an undeployed state to a deployed state, the distance between the two distal arms increases. This causes any anatomical tissue between two distal arms to spread along the straight line between two distal arms Spreading device  3620  can be deployed by a variety of methods including, but not limited to removing spreading device  3620  from a sheath or cannula, etc. In one embodiment, spreading device  3620  is made from a shape memory material such as Nitinol. In this embodiment, spreading device  3620  is maintained in the undeployed state by maintaining anchor device  3620  in a temperature lower than the transition temperature of the super-elastic material. Spreading device  3620  is converted to the deployed state by implanting spreading device  3620  in a patient such that the device is warmed to the body temperature which is above the transition temperature of the super-elastic material. Stretching of prostate gland tissue can be used to eliminate or reduce the compression of the urethra by an enlarged prostate gland or to prevent cut edges of a cut from rejoining. 
     More than one spreading device  3620  may be used to treat the effects of an enlarged prostate or to eliminate or reduce the compression of the urethra by an enlarged prostate gland or to prevent cut edges of a cut from rejoining. 
       FIGS. 37A through 37K  show an embodiment of a method of treating prostate gland disorders by cutting a region of the prostate gland using the devices described in  FIG. 33A through 33E . In  FIG. 37A , introducer device  3300  is introduced in the urethra. It is advanced through the urethra such that the distal tip of introducer device  3300  is located in the prostatic urethra. Thereafter, injecting needle  3330  is introduced through introducer device  3300 . The distal tip of injecting needle  3330  is advanced such that injecting needle  3330  penetrates the prostate gland. Injecting needle  3330  is then used to inject a substance such as an anesthetic in the prostate gland. Thereafter, in  FIG. 37B , injecting needle  3330  is withdrawn from the anatomy. The distal region of introducer device  3300  is positioned near a region of the prostate gland to be punctured. Thereafter, in  FIG. 37C , first tubular element  3302  is bent or deflected with a bending or deflecting mechanism such as the bending mechanism in FIGS.  37 C″ and  37 C′″ to align the distal region of first tubular element  3302  along a desired trajectory of puncturing the prostate gland. 
     FIG.  37 C′ shows the proximal region of introducer device  3300 . A cystoscope  3700  is introduced through second stasis valve  3316  such that the distal end of cystoscope  3700  emerges through the distal end of introducer device  3300 . Cystoscope  3700  is then used to visualize the anatomy to facilitate the method of treating prostate gland disorders. 
     FIG.  37 C″ shows a perspective view of the distal region of an embodiment of introducer device  3300  comprising a bending or deflecting mechanism. In this embodiment, first tubular element  3302  comprises a spiral cut distal end and a pull wire. In FIG.  37 C′″, the pull wire is pulled by deflection dial  3310 . This deflects the distal tip of first tubular element  3302  as shown. 
     After the step in  FIG. 37C , guiding device  3338  is introduced through first tubular element  3302 . Guiding device  3338  is advanced through first tubular element  3302  such that the distal tip of guiding device  3338  penetrates into the prostate gland. In one method embodiment, guiding device  3338  is further advanced such that the distal tip of guiding device  3338  penetrates through the prostate gland and enters the urinary bladder. In one embodiment, distal region of guiding device  3338  comprises an anchoring element  3702 . Anchoring element  3702  is deployed as shown in  FIG. 37E . Thereafter, guiding device  3338  is pulled in the proximal direction till anchoring element  3702  is snug against the wall of the urinary bladder. Cystoscope  3700  can be used to visualize the steps of penetrating the prostate gland by guiding device  3338  and deploying anchoring element  3702 . If guiding device  3338  is not positioned in a satisfactory position, guiding device  3338  is pulled back in introducer device  3300 . The deflection angle of distal end of first tubular lumen  3302  is changed and guiding device  3338  is re-advanced into the urinary bladder. FIG.  37 E′ shows a perspective view of an embodiment of anchoring element  3702 . Anchoring element comprises a hollow sheath  3704 . Distal region of hollow sheath  3704  is attached to distal region of guiding device  3338 . A number of windows are cut in the distal region of hollow sheath  3704  such that several thin, splayable strips are formed between adjacent windows. Pushing hollow sheath  3704  in the distal direction causes splayable strips to splay in the radially outward direction to form an anchoring element. In  FIG. 37F , cutting device  3343  is advanced over guiding device  3338  into the prostate gland. In  FIG. 37G , cutting device  3343  is positioned in the prostate gland such that proximal marker band  3348  can be seen by cystoscope  3700  but distal marker band  3350  cannot be seen. 
     Thereafter, in  FIG. 37H , relative motion between outer sheath  3343  and inner sheath  3344  causes cutting wire  3352  to deploy outward in the axial direction. In one embodiment, this step is carried out by moving outer sheath  3343  in the distal direction while the inner sheath  3344  is stationary. In another embodiment, this step is carried out by moving inner sheath  3344  in the proximal direction while outer sheath  3343  is kept stationary. Also during step, electrical energy is delivered through cutting wire  3352  to cut tissue. In  FIG. 37I , cutting device  3343  is pulled in the proximal direction such that the deployed cutting wire  3352  slices through tissue. Thereafter, cutting wire  3352  is withdrawn again in cutting device  3343 . Cutting device  3343  is then removed from the anatomy. 
     In  FIG. 37J , plugging device  3354  is introduced over guiding device  3338  through the puncture or opening in the prostate gland. Thereafter, in  FIG. 37K , anchoring element  3702  is undeployed and guiding device  3343  is withdrawn from the anatomy. Thereafter, plugging device  3354  is used to deliver one or more plugging materials in the adjacent anatomy. The plugging materials can be used to plug or line some or all of the cuts or punctures created during the method. 
       FIGS. 38A to 38D  show various components of a kit for treating prostate gland disorders by compressing a region of the prostate gland.  FIG. 38A  shows the perspective view of an introducer device  3800 . Introducer device  3800  comprises an outer body  3801  constructed from suitable biocompatible materials including, but not limited to metals like stainless steel, Nichol plated brass, polymers like Pebax, Polyimide, Braided Polyimide, Polyurethane, Nylon, PVC, Hytrel, HDPE, PEEK and fluoropolymers like PTFE, PFA, FEP, EPTFE etc. Body  3801  comprises a working device lumen  3802 . Distal end of working device lumen  3802  emerges out of the distal end of body  3801 . Proximal end of working device lumen  3802  incorporates lock thread  3803  such that introducer device may join with other devices. Device lumen  3802  may comprise one or more side ports e.g. a first side port  3804  and a second side port  3805  for the introduction or removal of one or more fluids. 
       FIG. 38B  shows a perspective view of a bridge device  3806  constructed from suitable biocompatible materials including, but not limited to metals like stainless steel, Nichol plated brass, polymers like Pebax, Polyimide, Braided Polyimide, Polyurethane, Nylon, PVC, Hytrel, HDPE, PEEK and fluoropolymers like PTFE, PFA, FEP, EPTFE etc. Bridge device may insert into introducer lumen  3802  and lock into place by threadably mating thread lock  3807  with thread  3803 . Bridge may incorporate port  3808  for cystoscope with locking means  3809  that joins to cystoscope when inserted. Bridge device may incorporate one or more working lumens. Working lumen  3810  emerges out of the distal end of body  3806 . In one embodiment, distal end of working device lumen  3810  has a bent or curved region. Proximal end of lumen  3810  emerges from port  3811  that may incorporate fluid stasis valve  3812  and a luer lock. Working lumen  3813  emerges distally in straight fashion through blunt obturator  3814  at distal end of body  3806  and emerges proximally through second port that may incorporate fluid stasis valve and luer lock. 
       FIG. 38C  shows a perspective view of a distal anchor deployment device  3815  constructed from suitable biocompatible materials including, but not limited to polymers like Polycarbonate, PVC, Pebax, Polyimide, Braided Pebax, Polyurethane, Nylon, PVC, Hytrel, HDPE, PEEK, metals like stainless steel, Nichol plated brass, and fluoropolymers like PTFE, PFA, FEP, EPTFE etc. Deployment device  3815  comprises handle  3816 , which incorporates movable thumb ring pusher  3817  and anchor deployment latch  3818 ; and distal shaft  3819  which has trocar point  3820  at distal end. Mounted on distal shaft  3819  is distal anchor  3821  that incorporates tether  3822 . Tether  3822  can be made of suitable elastic or non-elastic materials including, but not limited to metals e.g. stainless steel 304, stainless steel 306, Nickel-Titanium alloys, suture materials, titanium etc. or polymers such as silicone, nylon, polyamide, polyglycolic acid, polypropylene, Pebax, PTFE, ePTFE, silk, gut, or any other monofilament or any braided or mono-filament material. Proximal end of tether  3822  may incorporate hypotube  3823 . Distal anchor  3821  is constructed from suitable biocompatible materials including, but not limited to metals e.g. stainless steel 304, stainless steel 306, Nickel-Titanium alloys, titanium etc. or polymers e.g. Pebax, Braided Pebax, Polyimide, Braided Polyimide, Polyurethane, Nylon, PVC, Hytrel, HDPE, PEEK, PTFE, PFA, FEP, EPTFE etc. Deployment device  3815  is inserted into bridge working lumen  3810 . Advancement of thumb ring  3817  extends distal shaft  3819  through distal end of working lumen  3810 , preferably into tissue for deployment of distal anchor  3821 . Depth of distal shaft deployment can be monitored on cystoscope by visualizing depth markers  3824 . Once distal shaft  3819  is deployed to desired depth, anchor deployment latch  3818  is rotated to release distal anchor  3821 . Retraction of thumb ring  3817  then retracts distal shaft  3819  while leaving distal anchor  3821  in tissue. Bridge  3806  is then disconnected from introducer device  3800  and removed. 
       FIG. 38D  shows the proximal anchor delivery tool  3825  constructed from suitable biocompatible materials including, but not limited to polymers like Polycarbonate, PVC, Pebax, Polyimide, Braided Pebax, Polyurethane, Nylon, PVC, Hytrel, HDPE, PEEK, metals like stainless steel, Nichol plated brass, and fluoropolymers like PTFE, PFA, FEP, EPTFE etc. Proximal anchor delivery tool  3825  comprises handle  3826 , which incorporates anchor deployment switch  3827  in slot  3828  and tether cut switch  3829 ; and distal shaft  3830  which houses hypotube  3831 . Lumen of hypotube  3831  emerges proximally at port  3832  which may incorporate a luer lock. Mounted on the hypotube and distal shaft is the proximal anchor  3833  with cinching hub  3834 . Proximal anchor  3833  is constructed from suitable biocompatible materials including, but not limited to metals e.g. stainless steel 304, stainless steel 306, Nickel-Titanium alloys, titanium etc. or polymers e.g. Pebax, Braided Pebax, Polyimide, Braided Polyimide, Polyurethane, Nylon, PVC, Hytrel, HDPE, PEEK, PTFE, PFA, FEP, EPTFE or biodegradable polymers e.g. polyglycolic acid, poly(dioxanone), poly(trimethylene carbonate) copolymers, and poly (ε-caprolactone) homopolymers and copolymers etc.  FIG. 38E  shows a close-up perspective view of proximal anchor  3833  mounted on hypotube  3831  and distal shaft  3830  of proximal anchor delivery tool  3825 . Hypotube  3831  biases open the cinching lock  3835  of cinching hub  3834 . In order to deploy proximal anchor  3833 , hypotube  3823  is loaded into hypotube  3831  until it exits proximal port  3832 . Hypotube  3823  is then stabilized while proximal anchor delivery tool  3825  is advanced into introducer device lumen  3802  and advanced to tissue target. Because hypotube  3831  biases open cinching lock  3835 , the proximal anchor delivery tool travels freely along tether  3822 . Once proximal anchor  3833  is adequately apposed to urethral wall of prostate, anchor deployment switch  3827  is retracted. During retraction of switch  3827 , hypotube  3831  is retracted proximal to cinching hub  3834  and tether  3822  is tightened. When switch  3827  is fully retracted or desired tension is accomplished, tether  3822  is cut within cinching hub  3834  by advancing cutting switch  3829 . 
     Any of the anchoring devices disclosed herein may comprise one or more sharp distal tips, barbs, hooks etc. to attach to tissue. 
     Various types of endoscopes can be used in conjunction with the devices disclosed herein such as flexible scopes that are thin, flexible, fibre-optic endoscopes and rigid scopes that are thin, solid, straight endoscopes. The scopes may have one or more side channels for insertion of various instruments. Further they may be used with in conjunction with standard and modified sheaths intended for endoscopic and transurethral use. 
     Local or general anesthesia may be used while performing the procedures disclosed herein. Examples of local anesthetics that can be used are anesthetic gels e.g. lidocaine gels in the urethra; combination of anesthetic agents e.g. combination of lidocaine and bupivacaine in the urethra; spinal anesthetics e.g. ropivacaine, fentanyl etc.; injectable anesthetics e.g. 1% lidocaine solution injected into the neurovascular bundles, the genitourinary diaphragm, and between the rectal wall and prostate; etc. 
     An optional trans-rectal ultrasound exam may be performed before and/or during the procedures disclosed herein. In this exam, a device called ultrasound transducer is inserted into the rectum. The ultrasound transducer is then used to image the prostate gland PG using ultrasound waves. The devices may be modified so that they are more visible under ultrasound such as etched surfaces. Other imaging devices may also be optionally used such as MRI, RF, electromagnetic and fluoroscopic or X-ray guidance. The anchoring devices or delivery devices may contain sensors or transmitters so that certain elements may be tracked and located within the body. The tethering devices may be used as cables to temporarily transmit energy to the distal and/or proximal anchors during deployment. 
     The invention has been described hereabove with reference to certain examples or embodiments of the invention but various additions, deletions, alterations and modifications may be made to those examples and embodiments without departing from the intended spirit and scope of the invention. For example, any element or attribute of one embodiment or example may be incorporated into or used with another embodiment or example, unless to do so would render the embodiment or example unsuitable for its intended use. Also, where the steps of a method or process are described, listed or claimed in a particular order, such steps may be performed in any other order unless to do so would render the embodiment or example un-novel, obvious to a person of ordinary skill in the relevant art or unsuitable for its intended use. All reasonable additions, deletions, modifications and alterations are to be considered equivalents of the described examples and embodiments and are to be included within the scope of the following claims.