JP6301909B2 - Stretch valve balloon catheter and method for producing and using the same - Google Patents

Description

  The present invention relates to catheters, and more particularly to balloon catheters that are automatically deflated with a stretch valve and methods for using and manufacturing such catheters.

  There are a number of conventional balloon catheters in the prior art. Some catheters are used, for example, during surgery to treat drainage from the patient's bladder and / or the bladder and / or urethra or prostate. For example, a common balloon catheter called RUSCH® Foley catheter is widely used today for the treatment and drainage of a patient's bladder. The Foley catheter is shown in FIG. 1, and includes a multi-lumen shaft 1 disposed in the urethra 10, a balloon portion 3 disposed at the distal end of the shaft 1, and a distal end of the balloon 3. It has a fluid drain portion 4 that is arranged and a curved or straight distal guide tip 5 at the most distal end of the entire catheter. When properly attached, the proximal side of the inflated balloon 3 rides on the inner wall 31 of the bladder 30 and completely closes the urethral bladder transition 11 connecting the bladder 30 and the urethra 10. In such an arrangement, the fluid drain portion 4 allows for continuous drainage of the bladder 30 and the balloon 3 substantially completely prevents the catheter from exiting the bladder. This ideally inserted arrangement is shown in FIG. As used herein, a fluid can be either a liquid or a gas. Exemplary fluids for inflating the balloon 3 are saline, sterile water, air, or carbon dioxide gas. Exemplary fluids drained by the catheters described herein include urine and blood.

  Basically, a catheter has a tubular body and has two lumens therethrough. The larger lumen communicates (distally) with the bladder and flows (proximally) into an extracorporeal bag for final disposal, not shown. The smaller lumen is used to expand (and deflate) the balloon 3 with sterile water using a syringe (typically) attached to an inflation lumen fitting 260 (see, eg, FIG. 3). For example, when dilated in the bladder, the catheter is substantially unable to exit the urethra during use.

  In the conventional balloon 3, the balloon 3 has a substantially constant balloon thickness. Balloon 3 is secured to the outer surface of a fluid drainage line (not shown in FIG. 1) and is intended not to be removed from or ruptured there unless the amount of expansion is enormous. If such happens, the balloon material will cleave at random locations based on microscopic fractures or weaknesses in the material itself. Such tearing should not occur under any circumstances when used on a patient.

  Prior art catheters are not constructed to prevent urethral rupture during catheter implantation surgery, nor are they constructed to break in a predetermined manner. Prior art catheters are situations where surgery is required to surgically remove the balloon, either with a syringe similar to an expanded one, or after a doctor's diagnosis that the balloon cannot be deflated. Is designed to contract only when actively contracting.

  Worldwide, more than 96 million indwelling catheters are sold annually. 24 million catheters are sold to hospitals in the United States. There are a myriad of complications associated with these catheters that should be prevented. These complications cause hospitalization, excessive bleeding, mortality, and increased morbidity. They also increase costs and burdens in a health system that is already under stress.

  Complications arise from several different mechanisms. The first and perhaps most often is improper placement of the catheter. Due to the unique anatomy of the male urethra, it can be difficult to place a urinary catheter for urine drainage. A problem arises when a doctor, technician, or nurse misunderstands that the catheter is not in the proper position but is actually in the proper position. The proper position of the catheter is with the balloon placed in the bladder. In this position, the tip distal to the balloon is placed in the bladder and used to drain from within the bladder.

  However, the physician or technician has no visual assistance to place the catheter into the bladder 30 at the ideal location. As shown in FIG. 1, the wall 40 that defines the urethral bladder transition 11 is very short in the longitudinal direction of the urethra 10. If the doctor inserts the catheter too deeply into the bladder 30, the balloon expansion will not be damaged, but there is a possibility of leakage around the balloon 3. This helps to actually smooth the urethra 10 under normal conditions. In such a case, the proximal side of the balloon 3 is placed in contact with the urethral bladder transition section 11 by gently moving the shaft 1 in the proximal direction. The bladder 30 then easily expands and extends to supplement the balloon 3. Normal bladder capacity is 400 cc to 500 cc. Although larger balloons may be used, typical balloon volumes are about 10 cc to 12 cc. A typical balloon is 5 cc, but many clinicians place 10 cc of water into the balloon for expansion. With 5 cc of water in the balloon, the diameter is about 2 cm, and at 10 cc, the diameter is about 2.5 cm.

  Complications arise when the technician and / or nurse expands the balloon without the balloon in the bladder. If the technician does not insert the catheter deep enough, the balloon 3 is expanded within the urethra 10. Although this is common, it is a condition that should be avoided even if it is not correct, and is often the cause of bladder infections that occur during hospital or clinic visits. Infectious diseases occur because the expansion of the bladder 3 in the urethra 10 causes the urethra 10 to overextend and tear. Although the urethra 10 is a flexible tube, it has a limit that allows it to be safely extended from the inside. The balloon outer diameter / circumference of almost all balloon catheters well exceeds the safe extension limit of the urethra 10. Therefore, if the balloon catheter is not inserted sufficiently deep, expansion of the balloon 3 can seriously injure the urethra 10. This is especially true for elderly patients who have a urethra that is less elastic than younger patients. Equally important is also changes in the anatomy of older men, particularly the prostate part of the urethra. As the patient ages, the prostate grows, and sometimes the catheter cannot be advanced through the prostate part of the urethra. When this happens, the technician expands the balloon in the urethra without inserting the catheter into the bladder. Alternatively, because of the stenosis, i.e. scar tissue, the catheter is stopped and additional pressure tears the urethral wall and creates new unintended holes. Both of these inappropriate insertions cause massive bleeding and serious disability.

  Balloons with rubbery elasticity in today's catheter products require relatively high pressure to begin to expand and expand to the outer diameter shape expected upon overexpansion. Thus, when not properly placed in the urethra, rapid expansion with high pressure causes the balloon to tear the surrounding membrane called the mucous membrane. When the urethra 10 is torn in this manner, bleeding occurs, allowing bacteria to enter the bloodstream at the laceration site, resulting in subsequent bladder infection. Massive bleeding can be life-threatening. The urethra can usually be expanded a few millimeters, but when the balloon is inflated, this expansion is usually a few centimeters. Also, if the balloon expansion fluid is not drained sufficiently and quickly after improper placement, accidental or deliberate pulling of the catheter from the outside can cause significant physical damage to the patient, and Actually wake up.

  Especially in patients undergoing anticoagulant therapy, life-threatening bleeding can and does occur. In addition, as seen in immunocompromised patients and the elderly, urine infection can cause severe infections (eg, sepsis) that can cause bacteria to enter the bloodstream and often lead to death. Even if the patient survives the first trauma, long-term complications such as stenosis can and do occur. Stenosis narrows the urinary passageway and usually requires additional procedures and surgery to heal.

  Other mechanisms of catheter-induced damage are inadvertent tubing manipulation or balloon removal that occurs when the catheter is pulled from outside the patient's body due to abrupt pulling or pulling. This usually occurs when a patient walks around or moves from a bed to a portable toilet or bathroom. When the patient is still moving, the tubing may become fixed for some reason. At that time, the balloon is suddenly pulled, pulling the balloon into the urethra, creating a laceration in the urethra, which is terrible. Causes pain and massive bleeding. Damage caused by removal of an expanded balloon catheter due to inappropriate, inadvertent, premature, or a combination of these is called iatrogenic damage (also called in-hospital damage). Because hundreds of thousands of these iatrogenic injuries occur each year, these costs are not only for patient safety, but the costs charged to the health care industry for each type of damage. Everything must be prevented.

  Yet another situation occurs when a patient intentionally pulls on a catheter, thereby causing self-induced urethral pain and damage. This is usually the case for patients who are in a state of confusion, such as those in a rehabilitation facility with a disease or cognitive impairment problem such as Alzheimer's disease, or other illnesses that make the patient unable to understand the need to wear a catheter. Occur. Confusion occurs when the patient has convulsions, causing pain and a strong urge to urinate. During convulsions, patients who are confused often often tugs and pulls, thereby causing damage. Similar to iatrogenic damage, these self-induced damages must also be prevented. In the specific case of damage (either iatrogenic or self-inducible) caused by pulling out the catheter while the balloon is inflated, the hospital will identify such damage as a “never event. events) ”, ie, events that should never occur. Under such circumstances, insurance generally does not compensate for the resulting significant medical costs.

  The injuries described herein cause serious disability not only in men but also in women's bladder and urethra. Injury may occur after surgery, which makes the disorder more serious. One common situation in which injury occurs is when the patient is being dosed with morphine or other analgesics that confuse the patient and prevent intelligent decision making. A patient who feels a foreign object in the urethra and is confused does not know that it should be left alone, but instead puts a strong pull that causes damage to it. These injuries are documented in detail and are not limited to adults. Many injuries have also been recorded for pediatric patients.

  Usually, the diagnosis of patient-caused catheter damage is time consuming. Immediately after the diagnosis of injury, the technician needs to contract the catheter. However, once the urethra is lacerated, it is very difficult to replace a broken catheter with another catheter, and in fact worsens the damage. Sometimes, once damage occurs, the patient must be transported to the operating room to replace the urethral drainage tube. Currently, in certain situations during home care, catheters and leg bags are routinely used, so this situation is not limited to hospitals, but also occurs in medical facilities and patient homes.

  Many of the latest catheter technologies are focused on controlling urinary tract infections caused by catheters, which are usually the most common catheter-related complications of injury. One example of such a technique is impregnating the catheter with an antibacterial or antibiotic agent. However, these improvements do not help prevent the damage described herein.

  Accordingly, it would be beneficial to provide a balloon catheter that does not expand beyond the rupture limit of the urethra and that deflates in certain desired ways under certain conditions.

  Thus, it comprises a stretch valve that overcomes the challenges of the known devices and methods of this general type described hereinabove and that quickly and rapidly deflates when drawn before balloon deflation based on the physician's plan. It would be desirable to provide a pressure balloon catheter that automatically contracts, as well as methods of making and using the catheter.

  In view of the foregoing and other objectives, in accordance with the present invention, an outer diameter, a distal tip, a catheter proximal end having a drain end, an inflation proximal end, a hollow stretch valve, and A flexible multi-lumen shaft is provided. A multi-lumen shaft defines a balloon lumen and a drain lumen that extends through the shaft and is operable to drain fluid near the distal tip therethrough and out of the proximal end of the drain. A distal hollow balloon portion having at least one inflation port fluidly coupled to the interior of the balloon, wherein the balloon portion is exposed through the at least one inflation port to a diameter greater than the outer diameter of the shaft. A distal hollow balloon portion operable to expand in an orientation and at least one inflation lumen parallel to the drain lumen and fluidly coupled to the at least one inflation port, the at least one inflation At least one lumen operable to expand the interior of the balloon with an expanding fluid; Defining the inflation lumen, and a drainage port. The drainage port fluidly couples at least one of the interior of the balloon and at least one inflation lumen to at least one of the drain lumen and the periphery of the balloon portion. A hollow stretch valve is coaxially disposed in the at least one inflation lumen and is operable to allow expansion fluid to pass therethrough and disposed in the at least one inflation lumen so that the fluid is in a drainage port at steady state. A fixed portion having a valve distal end and a valve proximal end and fixedly coupled to at least one of the valve distal end and the valve proximal end within at least one inflation lumen. And having a sliding portion slidably disposed within the at least one inflation lumen at the other of the valve distal end and the valve proximal end, in the extended state where the catheter proximal end is extended, The moving part slides within the at least one inflation lumen and the expansion fluid is drained A so as to be able to pass through.

  With the objectives of the present invention in mind, a flexible, multi-piece having an outer diameter, a distal tip, a catheter proximal end having a drain end, an inflation proximal end, and a hollow stretch valve. There is further provided a safety catheter comprising a hollow shaft. A multi-lumen shaft defines a balloon lumen and a drain lumen that extends through the shaft and is operable to drain fluid near the distal tip therethrough and out of the proximal end of the drain. A distal hollow balloon portion having at least one inflation port fluidly coupled to the interior of the balloon, wherein the balloon portion is exposed through the at least one inflation port to a diameter greater than the outer diameter of the shaft. A distal hollow balloon portion operable to expand in an orientation and at least one inflation lumen parallel to the drain lumen and fluidly coupled to the at least one inflation port, the at least one inflation At least one lumen operable to expand the interior of the balloon with an expanding fluid; Defining the inflation lumen, and a drainage port for fluidly connecting the internal balloon to the drain lumen. A hollow stretch valve is positioned coaxially to the drain lumen and is operable to allow fluid to pass therethrough, and is positioned at the drain lumen to prevent fluid from passing through the drainage port in steady state conditions. A distal end having a distal end and a proximal valve end, having a fixed portion fixedly coupled to one of the distal valve end and the proximal valve end within the drain lumen, and the distal valve end within the drain lumen And a sliding portion slidably disposed on the other of the proximal end of the valve, and in the extended state where the proximal end of the catheter is extended, the sliding portion slides and expands within the drain lumen. Allow the working fluid to pass through the drainage port.

  In view of the foregoing and other objectives, in accordance with the present invention, an outer diameter, a distal tip, a catheter proximal end having a drain end, an inflation proximal end, a hollow stretch valve, and A flexible multi-lumen shaft is provided. A multi-lumen shaft defines a balloon lumen and a drain lumen that extends through the shaft and is operable to drain fluid near the distal tip therethrough and out of the proximal end of the drain. A distal hollow balloon portion having at least one inflation port fluidly coupled to the interior of the balloon, wherein the balloon portion is exposed through the at least one inflation port to a diameter greater than the outer diameter of the shaft. A distal hollow balloon portion operable to expand in an orientation and at least one inflation lumen parallel to the drain lumen and fluidly coupled to the at least one inflation port, the at least one inflation At least one lumen operable to expand the interior of the balloon with an expanding fluid; Defining the inflation lumen, and a drainage port. The drainage port fluidly couples at least one of the interior of the balloon and at least one inflation lumen to at least one of the drain lumen and the periphery of the balloon portion. A hollow stretch valve is coaxially disposed in the at least one inflation lumen and is operable to allow expansion fluid to pass therethrough and disposed in the at least one inflation lumen so that the fluid is in a drainage port at steady state. A fixed portion having a valve distal end and a valve proximal end and fixedly coupled to at least one of the valve distal end and the valve proximal end within at least one inflation lumen. And having a sliding portion slidably disposed within the at least one inflation lumen at the other of the valve distal end and the valve proximal end, in the extended state where the catheter proximal end is extended, The moving part slides within the at least one inflation lumen and the expansion fluid is drained A so as to be able to pass through. The multi-lumen shaft has a spread distal to the coupling portion of the fixed portion, which is relatively easy to extend than at least a portion of the spread-proximal multi-lumen shaft.

  With the objectives of the present invention in mind, a flexible, multi-piece having an outer diameter, a distal tip, a catheter proximal end having a drain end, an inflation proximal end, and a hollow stretch valve. There is further provided a safety catheter comprising a hollow shaft. A multi-lumen shaft defines a balloon lumen and a drain lumen that extends through the shaft and is operable to drain fluid near the distal tip therethrough and out of the proximal end of the drain. A distal hollow balloon portion having at least one inflation port fluidly coupled to the interior of the balloon, wherein the balloon portion is exposed through the at least one inflation port to a diameter greater than the outer diameter of the shaft. A distal hollow balloon portion operable to expand in an orientation and at least one inflation lumen parallel to the drain lumen and fluidly coupled to the at least one inflation port, the at least one inflation At least one lumen operable to expand the interior of the balloon with an expanding fluid; Defining the inflation lumen, and a drainage port for fluidly connecting the internal balloon to the drain lumen. A hollow stretch valve is positioned coaxially to the drain lumen and is operable to allow fluid to pass therethrough, and is positioned at the drain lumen to prevent fluid from passing through the drainage port in steady state conditions. A distal end having a distal end and a proximal valve end, having a fixed portion fixedly coupled to one of the distal valve end and the proximal valve end within the drain lumen, and the distal valve end within the drain lumen And a sliding portion slidably disposed on the other of the proximal end of the valve, and in the extended state where the proximal end of the catheter is extended, the sliding portion slides and expands within the drain lumen. Allow the working fluid to pass through the drainage port. The multi-lumen shaft has a spread distal to the coupling portion of the fixed portion, which is relatively easy to extend than at least a portion of the spread-proximal multi-lumen shaft.

  In view of the foregoing and other objectives, a safety catheter is provided according to the present invention that includes a flexible multi-lumen shaft and a hollow stretch valve. The flexible multi-lumen shaft has an outer diameter, a distal tip, a shaft proximal portion, and a catheter proximal end comprising a drain proximal end and an inflation proximal end. A multi-lumen shaft defines a balloon lumen and a drain lumen that extends through the shaft and is operable to drain fluid near the distal tip therethrough and out of the proximal end of the drain. A distal hollow balloon portion having at least one inflation port fluidly coupled to the interior of the balloon, wherein the balloon portion is exposed through the at least one inflation port to a diameter greater than the outer diameter of the shaft. A distal hollow balloon portion operable to expand in an orientation and at least one inflation lumen parallel to the drain lumen and fluidly coupled to the at least one inflation port, the at least one inflation At least one lumen operable to expand the interior of the balloon with an expanding fluid; And inflation lumen, defines a drainage port for fluidly connected to at least one drain lumen of the balloon interior and at least one inflation lumen. A hollow stretch valve is coaxially disposed in the drain lumen and is operable to allow fluid to pass therethrough. The stretch valve has a radially self-expanding proximal portion that is fixedly connected within the drain lumen by self-expansion, a flexible intermediate portion that can move in the longitudinal direction within the drain lumen, and a drain lumen. A distal plug that is movably disposed to prevent fluid from passing through the drainage port in a steady state and is slidably disposed within the drain lumen, wherein the proximal end of the catheter is extended The distal plug has a distal plug that slides within the drain lumen to allow expansion fluid to pass through the drainage port.

  With the objective of the present invention in mind, there is further provided a safety catheter comprising a safety catheter that includes a flexible multi-lumen shaft and a hollow stretch valve. The multilumen shaft has an outer diameter, a distal tip, a shaft proximal portion, and a catheter proximal end with a drain end and an inflation end. A multi-lumen shaft defines a balloon lumen and a drain lumen that extends through the shaft and is operable to pass fluid near the distal tip through and out of the drain end. A distal hollow balloon portion having at least one inflation port fluidly coupled to the interior of the balloon, the balloon portion facing outwardly through the at least one inflation port to a diameter greater than the outer diameter of the shaft A distal hollow balloon portion operable to expand and at least one inflation lumen parallel to the drain lumen and fluidly coupled to the at least one inflation port, the at least one inflation lumen At least one operable to expand the interior of the balloon with an expanding fluid Defining the inflationary lumen and a drainage port for fluidly connecting the internal balloon to the drain lumen. A hollow stretch valve is coaxially disposed in the drain lumen and is operable to allow fluid to pass therethrough. The stretch valve has a radially self-expanding proximal portion that is fixedly connected within the drain lumen by self-expansion, a flexible intermediate portion that can move in the longitudinal direction within the drain lumen, and a drain lumen. A distal plug that is movably disposed to prevent fluid from passing through the drainage port in a steady state and is slidably disposed within the drain lumen, wherein the proximal end of the catheter is extended The distal plug has a distal plug that slides within the drain lumen to allow expansion fluid to pass through the drainage port.

According to another feature of the invention, the stretch valve is in an extended state when a tensile force of about 1 pound (4.448 Newtons) to about 15 pounds (66.72 Newtons) is applied to the proximal shaft portion. Have According to a further feature of the present invention, the stretch valve is in an extended state when a tensile force of about 1 pound (4.448 Newton) to about 5 pounds (22.24 Newton) is applied to the proximal shaft portion. Have. In accordance with an additional feature of the present invention, the stretch valve is configured when a tensile force of about 1.5 pounds (6.672 Newtons) to about 2 pounds (8.896 Newtons) is applied to the proximal shaft portion. , Has an extended state. According to an additional feature of the invention, when the balloon portion is inflated with fluid and a tensile force greater than about 15 pounds is applied to the proximal shaft portion, the stretch valve fills the stretched state, thereby expanding. Shrink the hollow balloon. According to yet another aspect of the present invention, when the balloon portion is inflated with fluid and a tensile force greater than about 5 pounds (22.24 Newtons) is applied to the axial proximal portion, the stretch valve is in an extended state. Fill and thereby deflate the expanded hollow balloon. According to yet a further feature of the present invention, when the balloon portion is inflated with fluid and a tensile force greater than about 2 pounds (8.896 Newtons) is applied to the axial proximal portion, the stretch valve satisfies the extended condition. , Thereby deflating the expanded hollow balloon. According to a further feature of the present invention, the drainage port includes at least one of the interior of the balloon and at least one inflation lumen, a drain lumen, a proximal periphery of the balloon portion, and a distal portion of the balloon portion. Fluidly coupled to at least one of the surroundings. According to another feature of the invention, the self-expanding proximal portion of the hollow stretch valve is proximal to the proximal end of the balloon. According to yet another feature of the invention, the self-expanding proximal portion and the flexible intermediate portion are formed by a single coil having different properties selected from at least one of pitch and diameter. . According to a further additional feature of the invention, the drainage port fluidly couples at least one of the balloon interior and at least one inflation lumen to at least one of the drain lumen and the periphery of the balloon portion. A plurality of drainage ports. According to yet another aspect of the present invention, the drainage port fluidly couples the balloon interior and inflation lumen to the drain lumen. According to another feature of the invention, the self-expanding proximal portion of the hollow stretch valve is proximal to the proximal end of the balloon. According to yet another feature of the invention, the self-expanding proximal portion and the flexible intermediate portion are formed by a single coil having different properties selected from at least one of pitch and diameter. . According to an additional feature of the invention, the drainage port is a plurality of drainage ports, each fluidly connecting the interior of the balloon to the drain lumen, and a hollow stretch valve disposed on the drain lumen; A distal plug that prevents fluid from passing through a plurality of drainage ports in a steady state and is slidably disposed within a drain lumen, wherein the distal plug is in an extended state in which the catheter proximal end is extended. A distal plug that slides within the drain lumen to allow expansion fluid to pass through the plurality of drainage ports.

  The low-pressure balloon catheter of the present invention, for example, by automatically deflating the balloon before injury occurs when forced to withdraw from the bladder or dilated within the urethra, Prevent damage. The stretch-valve balloon catheter of the present invention prevents damage by automatically deflating the balloon before damage occurs, for example when forced to be withdrawn from the bladder prior to manual deflation as planned by the physician. . Although the catheter of the present invention makes it a safe device for urine drainage, the present invention can also be used in any surgery that uses a balloon to occlude a cavity. Examples of these surgeries include coronary and peripheral blood vessels such as aorta and limb blood vessels. Balloon dilation in other lumens such as the ureter and esophagus are also candidates for use with the catheter of the present invention. Further, the pressure release mechanism can be used for any fluid or air filled instrument such as a tissue dilator, transdermal device, and the like.

  Some embodiments of the present invention utilize valves (eg, slit valves or stretch valves) that can be reused in use. In an embodiment without such a valve, the present invention is a disposable post-contraction catheter. Such disposable catheters can no longer be used when contracted, but the rapid contraction action protects the patient from severe damage and the cost of replacing the catheter is compared to the enormous cost of treating the catheter-induced damage. Is minimal. Prevention of such damage is becoming increasingly important because damage is a daily occurrence. The increase occurs for a number of reasons. First, a greater proportion of the population is aging. Next, there is a current trend to recruit unskilled healthcare workers to perform more surgery and be responsible for treatment. These both save hospital and physician costs. The shortage of nursing professionals (eg, RN) has exacerbated this trend. The current trend is to use nursing professionals for more roles such as drug management and administration. This leaves the task of obtaining vital signs and catheter insertion to the least skilled technician. Under such circumstances, further damage can and does occur. Finally, complications related to catheters are becoming more severe due to increased use of anticoagulants such as PLAVIX®, which is well prescribed for the treatment of cardiovascular diseases.

  Yet another complication resulting from a standard Foley catheter is that the balloon does not deflate when the deflation mechanism is activated. This situation can occur, for example, because the wrong fluid is used to expand the balloon, or often occurs when fluids such as saline crystallize. Occasionally, the ability to deflate the catheter may be hindered because the drainage channel used to deflate the balloon is clogged, often seen when the catheter is left too long. Treatment of such situations includes invasive procedures that involve passing a needle or other sharp object somewhere through the body cavity to rupture the balloon and thus remove the catheter. included. This procedure is not desirable and should be avoided if possible. Yet another possible complication can occur when the patient has a stenosis, i.e., scar tissue, in the urethra that prevents passage of the catheter. When the technician faces stenosis, it appears to the technician that the catheter does not move toward the bladder. As a result, the technician uses excessive force to push the catheter into the bladder, thereby resulting in a laceration that forms its through hole in the penis and prostate tissue. As is obvious, this situation involves massive bleeding and the need for additional therapeutic procedures and surgery.

  With the low pressure or valved self-deflating balloon of the present invention, a technician, nurse, or physician may simply pull the catheter to automatically deflate the catheter, thus removing the patient from any further surgery. Let me escape.

  The added benefits of the present invention are not only secure, but also result in significant financial benefits. It is believed that the damage caused by the catheter is much more common than suggested by well-known records. Injuries related to catheters occur once a week in large hospitals in large cities. Usually, each incident substantially increases the cost of hospitalization as well as the length of hospitalization of the patient. Each case (which is not usually covered by insurance) can increase hospital costs by thousands of dollars, even tens of thousands or hundreds of thousands of dollars. This is especially true if the patient files a personal injury lawsuit against the hospital, doctors (doctors), staff, or a combination thereof. And if further surgery is needed to treat the damage caused by the catheter, not only will the increased cost to the hospital be substantial, but if the lawsuits occur as a result of the damage, the patient will be compensated for damages Can break into millions of dollars. The catheter and method of the present invention thus provide a safer catheter with the potential to save billions of dollars for the medical industry.

  In order to prevent the occurrence of urethral rupture due to premature balloon expansion too early and / or due to premature removal of the expanded balloon, the exemplary embodiments of the invention of the present application are various balloons. Provide safety valves. Such valves are configured to release expansion fluid from the balloon before damage occurs.

  The maximum internal pressure that a typical urethra can withstand without tearing and / or breaking is known and is referred to as the maximum urethral pressure. It is also possible to calculate how much pressure is applied to the outside of the balloon of the balloon catheter by measuring the pressure required to expand the balloon. Knowing these two values, it is possible to construct a balloon that quickly degrades or stops dilatation or both when the maximum urethral pressure is exceeded.

  For example, in the first exemplary embodiment, the balloon is typically some rubber, silicone, elastomer, or plastic, but if the balloon pressure exceeds the maximum urethral pressure, the balloon is instantaneously It can be made with a breaking point that shrinks. Since the cost of patient damage far exceeds that of disposable catheters, it has been confirmed and accepted that once a balloon breaks, the catheter cannot be used and must be discarded. Further, such balloons are limited to expansion with biologically safe fluids to prevent unwanted air / gas from entering the patient. However, if the air or other gas does not damage the patient, the fluid may be air or another gas.

  As an alternative to a safety valve that breaks after a single use, a multi-use pressure valve can be added to the balloon inflation lumen, and if the maximum urethral pressure in the balloon or balloon inflation lumen is exceeded, the drainage lumen It can also be installed to open. Such a valve may be located, for example, near or at the balloon inflation port. Any combination of the above embodiments is also envisioned.

  Another exemplary embodiment of the present invention provides a catheter having a balloon that expands substantially without pressure. As used herein, “virtually no pressure”, “zero-pressure” and “low-pressure” are used interchangeably and are generally standard. Defined as a range of pressure between atmospheric pressure and 0.3 atmosphere (5 psig). This is in contrast to “high pressure” greater than about 1.5 atmospheres (22 psig). With such a configuration, the zero pressure balloon can be deflated without substantial force. Thus, when a clinician attempts to expand a zero pressure balloon of the present invention within the urethra, the balloon does not expand at all. Similarly, if a balloon that has already been expanded in the bladder is pushed into the urethra, such contraction requires substantially no pressure to collapse the balloon and fit into the urethra. In both situations, damage to the urethra is completely prevented.

  A further exemplary embodiment of the present invention that prevents the occurrence of urethral rupture due to premature removal of the expanded balloon includes a balloon catheter comprising a stretch valve and a method for making and using such a valved catheter. provide. In these variations, the present invention takes advantage of the fact that premature removal of the expanded balloon catheter involves catheter extension on the proximal side of the balloon. A valved catheter may be configured with a release mechanism that is a function of extension. At a slight extension, the balloon will remain inflated, but if pulled beyond a predetermined limit, the valve will automatically open and drain the fluid filling the balloon. In some variations, the balloon can be refilled if contraction occurs without any damage. In either case, damage is prevented. The recitation of one exemplary embodiment herein in a sense separated from the other exemplary embodiments is intended to mean one embodiment that mutually excludes the other exemplary embodiments. Should not be done. The various exemplary embodiments of the safety catheter described herein can be used separately and independently, or they can be used together in any combination.

  While some variations are illustrated and described herein as being implemented in stretch valve balloon catheters and methods for making and using such catheters, they are not intended to limit the details shown. Absent. This is because various modifications and structural changes can be made therein without departing from the spirit of the invention and within the scope and scope of the claims. In addition, well-known elements of example embodiments of the invention have not been described in detail or are omitted so as not to obscure the relevant details of the invention. Other features which are considered as characteristic for the invention are set forth in the appended claims. As required, detailed embodiments of the present invention are disclosed herein. However, it is to be understood that the disclosed embodiments are merely exemplary of the invention, which can be implemented in various forms. Accordingly, the specific structural and mechanical details disclosed herein are not to be construed as limiting, but merely as a basis for the claims and substantially any suitable The detailed structure should be construed as a representative basis for teaching those skilled in the art to make various uses of the present invention. Further, the terms and phrases used herein are not intended to be limiting, but rather to provide an understandable description of the invention. The specification concludes with the claims that define the features of the invention deemed to be novel, but upon review of the following description in conjunction with the drawings in which like reference numbers have been carried forward, The invention will be better understood. The figures in the drawings are not to scale. Before further disclosure and description, it is to be understood that the terminology used herein is for the purpose of describing particular embodiments only and is not limiting. As used herein, the term “a” or “an” is defined as one or more. As used herein, the term “plurality” is defined as two or more. As used herein, the term “another” is defined as at least a second or a third or more. As used herein, the terms “including” and / or “having” are defined as comprising (ie, open language). As used herein, the term “coupled” is defined as being linked, although not necessarily directly and not necessarily mechanical. As used herein, the term “about orappropriately” applies to all numerical values, whether or not explicitly stated. These terms generally refer to a range of numbers that one of ordinary skill in the art would consider equivalent (ie, have the same function or result) to the listed values. In many cases, these words may include numbers rounded to the nearest significant figure. As used herein, “longitudinal” should be understood to mean a direction corresponding to the longitudinal direction of the catheter. Finally, the term “proximal” refers to the end of the catheter closest to the person inserting the catheter, usually the end of the catheter with the hub. The distal end of the catheter is the end furthest from the person inserting the catheter.

  Hereinafter, the present invention will be described in detail by way of exemplary embodiments and corresponding drawings. The drawings illustrate various exemplary embodiments of the invention by means of schematic diagrams that are not to scale.

1 is a schematic partial longitudinal sectional view of a prior art catheter ideally placed in the urethra and bladder of a male patient. FIG. 1 is a partially enlarged longitudinal sectional view of a distal portion of a first embodiment of a pressure limiting balloon catheter according to the present invention. FIG. FIG. 6 is a partially enlarged longitudinal sectional view of the proximal portion of a second embodiment of a pressure limiting balloon catheter according to the present invention. FIG. 4 is a partially enlarged cross-sectional view of a first alternative configuration of the safety valve of FIG. 3. FIG. 4 is a partially enlarged cross-sectional view of a second alternative configuration of the safety valve of FIG. 3. FIG. 4 is a partially enlarged cross-sectional view of a third alternative configuration of the safety valve of FIG. 3. It is the fragmentary sectional view which expanded further about the safety valve of FIG. FIG. 6 is an enlarged partial cross-sectional view of a fourth alternative configuration of the safety valve of FIG. 3. 1 is a partial perspective view, with parts omitted, of an exemplary embodiment of a zero pressure safety catheter according to the present invention. FIG. FIG. 10 is a radial cross-sectional view of a portion of the catheter at section line 10-10 of FIG. 9; FIG. 3 is a process flow diagram of an exemplary method for forming a zero pressure balloon according to the present invention. FIG. 3 is a process flow diagram of an exemplary method of attaching a zero pressure balloon according to the present invention. FIG. 3 is a partially enlarged perspective view of a distal portion of an exemplary embodiment of a zero pressure catheter according to the present invention. FIG. 14 is a radial cross-sectional view of the slit valve portion of the catheter taken along section line 14-14 in FIG. 13. FIG. 14 is a radial cross-sectional view of an alternative embodiment of the slit valve portion of the catheter at section line 15-15 of FIG. FIG. 3 is a partially enlarged view of a portion of a reversing balloon catheter according to the present invention in a position correctly inserted into the bladder, with a cross-sectional view and a partial perspective view. FIG. 17 is a partially enlarged view of a portion of the catheter of FIG. 16 being pulled distally from the bladder and beginning its inversion contraction, with a cross-sectional view and a partial perspective view. FIG. 17 is a partially enlarged view in which a part of the catheter of FIG. 16 in a state where the reverse contraction is completed is a cross-sectional view. FIG. 2 is a partially enlarged longitudinal cross-sectional view of a balloon portion of a prior art urinary catheter in an uninflated state. FIG. 20 is a partially enlarged longitudinal sectional view of the prior art urinary catheter of FIG. 19 in an expanded state in the bladder. 1 is a partially enlarged longitudinal cross-sectional view of a balloon portion of an exemplary embodiment of an automatically deflating stretch valve urinary balloon catheter according to the present invention with the balloon in an uninflated state. FIG. FIG. 22 is a partially enlarged longitudinal sectional view of the automatically deflating stretch valve urinary balloon catheter of FIG. 21 with the balloon inflated and the stretch valve not activated. FIG. 22 is a partially enlarged longitudinal cross-sectional view of the automatically deflating stretch valve urinary balloon catheter of FIG. 21 with the balloon in an inflated state and the stretch valve activated. FIG. 6 is a partially enlarged longitudinal sectional view of the balloon portion of another exemplary embodiment of an automatically deflating stretch valve urinary balloon catheter according to the present invention with the balloon in an uninflated state. FIG. 25 is a partially enlarged longitudinal cross-sectional view of the automatically deflating stretch valve urinary balloon catheter of FIG. 24 with the balloon in an inflated state and the stretch valve not activated. FIG. 25 is a partially enlarged longitudinal cross-sectional view of the automatically deflating stretch valve urinary balloon catheter of FIG. 24 with the balloon in an inflated state and the stretch valve activated. FIG. 10 is a partially enlarged longitudinal cross-sectional view of the balloon portion of yet another exemplary embodiment of an automatically deflating stretch valve urinary balloon catheter according to the present invention with the balloon in an uninflated state. FIG. 28 is a partially enlarged longitudinal cross-sectional view of the automatically deflating stretch valve urinary balloon catheter of FIG. 27 with the balloon inflated and the stretch valve not activated. FIG. 28 is a partially enlarged longitudinal cross-sectional view of the automatically deflating stretch valve urinary balloon catheter of FIG. 27 with the balloon in an inflated state and the stretch valve activated. FIG. 28 is a partially enlarged longitudinal sectional view of the automatically deflating stretch valve urinary balloon catheter of FIG. FIG. 28 is a partially enlarged longitudinal cross-sectional view of the automatically deflating stretch valve urinary balloon catheter of FIG. 27 rotated 90 degrees counterclockwise from its proximal end and with the stretch valve not activated. . FIG. 28 is a partially enlarged longitudinal cross-sectional view of the automatically deflating stretch valve urinary balloon catheter of FIG. 27 rotated 90 degrees counterclockwise from its proximal end and with the stretch valve activated. Of the balloon portion of yet another exemplary embodiment of an automatically deflating stretch valve urinary balloon catheter according to the present invention where the balloon is partially inflated and the stretch valve is not activated. It is a partial expanded longitudinal cross-sectional view. A portion of the balloon portion of a still further exemplary embodiment of an automatically deflating stretch valve urinary balloon catheter according to the present invention where the balloon is partially inflated and the stretch valve is not activated. It is an expanded longitudinal cross-sectional view. A portion of the balloon portion of a further exemplary embodiment of an automatically deflating stretch valve urinary balloon catheter according to the present invention where the balloon is partially inflated and the stretch valve is not activated. It is an expanded longitudinal cross-sectional view. Of the balloon portion of an additional exemplary embodiment of an automatically deflating stretch valve urinary balloon catheter according to the present invention where the balloon is partially inflated and the stretch valve is not activated. It is a partial expanded longitudinal cross-sectional view. A portion of the balloon portion of another exemplary embodiment of an automatically deflating stretch valve urinary balloon catheter according to the present invention where the balloon is partially inflated and the stretch valve is not activated. It is an expanded longitudinal cross-sectional view. Of the balloon portion of yet another exemplary embodiment of an automatically deflating stretch valve urinary balloon catheter according to the present invention with the balloon partially inflated and the stretch valve not activated. It is a partial expanded longitudinal cross-sectional view. 3 is a flowchart of an exemplary embodiment of a process for making a catheter according to the present invention. 6 is a flowchart of an exemplary embodiment of another process for making a catheter according to the present invention. Figure 3 is a flow chart of an exemplary embodiment of a further process for making a catheter according to the present invention. A portion of the balloon portion of another exemplary embodiment of an automatically deflating stretch valve urinary balloon catheter according to the present invention where the balloon is partially inflated and the stretch valve is not activated. It is an expanded longitudinal cross-sectional view. Balloon of yet another exemplary embodiment of an automatically deflating stretch valve urinary balloon catheter according to the present invention where the balloon is partially inflated and the longer stretch valve is not activated. It is a partial expanded longitudinal cross-sectional view of a part. 1 is an enlarged perspective view of an exemplary embodiment of a stretch valve for a urinary balloon catheter according to the present invention. FIG. FIG. 45 is a partially enlarged longitudinal cross-sectional view of the balloon portion of the automatically deflating stretch valve urinary balloon catheter with the stretch valve of FIG. 44 not activated and the balloon partially inflated. FIG. 6 is an enlarged perspective view of another exemplary embodiment of a stretch valve for a urinary balloon catheter according to the present invention. FIG. 47 is a partially enlarged longitudinal cross-sectional view of the balloon portion of an automatically deflating stretch valve urinary balloon catheter with the stretch valve of FIG. 46 not activated and the balloon partially inflated.

  The specification concludes with the claims that define the features of the invention deemed to be novel, but upon review of the following description in conjunction with the drawings in which like reference numbers have been carried forward, The invention will be better understood. Various embodiments of the invention are described herein. In many different embodiments, the features are similar. Therefore, to avoid redundancy, in some cases, repeated descriptions of these similar features may not be made. However, it is to be understood that the description of the first feature applies to similar features that follow, and thus each respective description is incorporated therein without being repeated as such. .

  Referring now in detail to the drawings, and more particularly to FIG. 2 in particular, a pressure limiting balloon catheter that does not expand beyond the tear limit of the lumen in which the catheter 100 is placed, eg, the lumen of the urethra. A first embodiment of 100 is shown.

  In order to prevent the occurrence of urethral rupture due to premature balloon expansion that is too early and / or due to premature removal of the expanded balloon, the invention of the present application includes a balloon 110 that includes a balloon safety valve 112. I will provide a. As described above, in a conventional catheter balloon 3 (see reference numbers 1 to 5 in FIG. 1), the high pressure balloon 3 is fixed to the outer surface of a fluid drainage lumen 120 (not shown in FIG. 1) to expand the amount of expansion. As long as is not enormous, it is intended not to be removed or ruptured from it. Such tearing should not occur under any circumstances when used on a patient. If such happens, the material of the balloon 3 will be cleaved at random locations based on microscopic breakage or weakness in the material itself, and after removal of the catheter 1 one or more of the balloons 3 will be removed. In addition to the risk of balloon fragmentation that can leave debris in the patient's body, the risk of severe injury to the patient by rupture is taken.

  For such conventional devices, the balloon 110 of the present invention is specially made to tear if the balloon 110 has a pre-determined pressure or such. Due to the presence of the balloon safety valve 112, a controlled tear occurs. Conventional balloons have a constant balloon wall thickness (before inflation). On the other hand, the balloon safety valve 112 in the first embodiment has a specified thickness reduction in the balloon thickness. This thinning creates a breakpoint or a selected breakpoint where there is a predetermined force on the balloon 110 or where the balloon 110 is specifically intended to break. Since the balloon 110 is made from a material having a known tear constant depending on its thickness (which is experimentally measured for different thicknesses of a given material prior to use in a patient), The balloon safety valve 112 of the present invention for application is adapted to break when the internal or external pressure of the balloon 110 reaches the maximum urethral pressure.

  In the embodiment shown in FIG. 2, the thickness reduction occurs as a first semicircular groove 114 near the proximal end of the balloon 110 or a second semicircular groove 116 near the distal end of the balloon 110. Or both. The grooves 114, 116 can have any cross-sectional shape including, for example, trapezoidal, triangular, square, or rectangular. Since rubber, plastic, and silicone materials tear well at thin cuts, a rather triangular shape or narrow bottom may be an exemplary configuration. To prevent the entire balloon 110 of the illustrated embodiment from being completely pulled away from the fluid drainage lumen 120, neither of the grooves 114, 116 extends around the entire circumference of the balloon 110. As shown to the left of the proximal groove 116 in FIG. 2, the groove 116 is not present on at least the arc portion 118 of the circumference of the balloon 110. The arcuate portion is defined sufficiently large that the balloon 110 cannot be completely pulled away from the catheter 100 (and creates the above-described undesirable fracture situation) when the catheter 100 is removed from the patient. The illustrated balloon safety valve 112 is therefore adapted to keep the balloon 110 integral after crushing and remain firmly connected to the catheter 100 so that any debris of the balloon 110 is not activated after the balloon safety valve 112 is actuated. Ensure that it does not remain in the patient's body. Alternatively, the groove may be parallel to the catheter axis and along the length of the balloon. This groove may be created by thinly peeling the balloon after attachment to the catheter, or by thinning the balloon as it is formed during extrusion or dip molding. In this embodiment, when the pressure exceeds a predetermined limit, the balloon breaks along the groove without producing debris.

  Note that the balloon 110 is typically expanded through an inflation lumen 130 having a proximal opening formed by one end of a luer connector (see 260 in FIG. 3). The end shown is connected to a distal end of an expansion device not shown, for example, a balloon 110 expansion syringe.

  In this first embodiment, the balloon can be, for example, an elastomer, rubber, silicone, or plastic. Once the balloon is broken, the catheter cannot be used and must be discarded. The balloon 110 in this embodiment is expanded with biologically safe fluid to prevent unwanted air, gas, or biologically unsafe fluid from entering the patient from breaking down in the patient's body. It must be. In certain situations where balloon catheters are used, air or gas will not harm the patient when released into the patient's body cavity. In such a situation, the expansion fluid may be, for example, pressurized air.

  Maximum urethral pressure can also be tailored to each patient. Based on the urethral pressure measuring device, the maximum urethral pressure of the patient can be measured before placing the catheter 100 therein. After the physician has access to a set of catheters 100 with different safety valve breakpoints, and after estimating, calculating, or grasping the patient's maximum urethral pressure, the physician can use a safety valve that is slightly or substantially less than the patient's maximum urethral pressure. A catheter 100 having a break point can be selected. Thus, if for any reason the pressure of the balloon 110 reaches the patient's maximum urethral pressure, the balloon 110 will be placed in the patient's maximum pressure, either due to overexpansion, improper placement, or premature removal, or a combination thereof. It is guaranteed to break before the lumen (especially the patient's urethra) and thus before any damage occurs.

  A second embodiment of a safety valve that breaks with a single use of the pressure limiting balloon catheter 200 is shown in FIG. Catheter 200 has a fluid drainage lumen 220, a balloon inflation lumen 230, and an auxiliary lumen 240. The fluid drainage lumen 220 is fluidly coupled to the body cavity (ie, the bladder 30) for draining fluid from the body cavity. The auxiliary lumen 240 can be used for any purpose, for example, to accommodate an irradiation line that supplies energy to the irradiation coil 2. The auxiliary lumen 240 can also be used to inject fluid into any distal portion of the catheter 200 or even into the body cavity itself. Balloon inflation lumen 230 begins in the exemplary embodiment with a proximal end that includes an expansion connector 260 that is part of a luer connector. The balloon inflation lumen 230 continues through the body of the catheter 200 into the balloon 110 and is fluidly coupled to the interior of the balloon 110.

  Alternatively or additionally, the balloon safety valve is fluidly coupled to the balloon inflation lumen 230. In a second embodiment of the safety valve 212, the valve 212 is integrally formed with the balloon inflation lumen 230 and (when not exceeding the maximum urethral pressure) in the balloon 110 or balloon inflation lumen 230 (not in the patient's body). It can also be installed open to the environment. Alternatively, and not shown, the valve 212 is integrally formed with the balloon inflation lumen 230 and opens into the drainage lumen 220 when the maximum intraurethral pressure is exceeded in the balloon 110 or balloon inflation lumen 230. It can also be installed. Further alternatives include releasing both within the environment and within the drainage lumen 220. Since this safety valve 212 is located near or at the balloon inflation port 260 in this configuration, the fluid used to expand the balloon does not enter the patient when the valve 212 is released.

  The safety valve 212 in the second embodiment may simply be a narrowing of the distance between the balloon inflation lumen 230 and the outer surface 250 of the catheter 220. In FIG. 3, the valve 212 has a rectangular cross section and extends in a direction away from the balloon inflation lumen 230. As shown in FIGS. 4, 5, and 6, respectively, the cross section can be triangular (three-dimensional pointed or pyramid), curved (three-dimensional circular or cylindrical), or trapezoid (three-dimensional). (Conical or rod-shaped). The cross section is shown in FIGS. 3 to 7 with the narrow portion protruding outward from the balloon inflation lumen 230. As an alternative, the constriction may begin on the outer surface of the catheter and extend inward toward the balloon inflation lumen 230. A further alternative may have a narrow that extends from both the inner lumen 230 and the outer surface of the catheter.

The cross section shown is merely illustrative. What is important is the thickness t between the bottom 213 of the valve 212 and the outer surface 250 of the catheter 220 as compared to the thickness T of the catheter body over the remaining balloon inflation lumen 230. An enlarged view of this thickness comparison is shown in FIG. As long as the thickness t is smaller than the thickness T (t <T), and as long as the force F _b required for breaking the balloon is larger than the force F _sv required for breaking the portion 213 of the safety valve 212 (F _b > F _sv ), the portion 213 of the safety valve 212 is substantially applied each time the pressure exerting a force F on the balloon inflation lumen 230 is greater than the force F _sv required to break the safety valve (F _sv > F) Guaranteed to break ,.

Based on this analysis, the force F _sv required to break the safety valve can be tailored to what the patient needs or the physician desires, and different sized valves are available for any operation. Yes, it can be provided in the form of a kit. Regardless of whether the standard maximum urethral pressure is used or the patient-specific maximum urethral pressure is measured and used, experiments are performed at various catheter thicknesses t prior to use on the patient to determine the safety valve 212 The pressure required for breaking the portion 213 may be determined. For example, ten different maximum urethral pressures can be grasped as desirable set values, and the thickness t can be changed so that the pressure required to break the ten types of thickness corresponds to the ten set value pressures. . As a result, if there are 10 catheters in such a kit, each having one of 10 thicknesses, the physician will have a maximum of 10 different for use on the patient. The urethral pressure value can be prepared.

  3-7 show a recess into the catheter wall, the recess may be in the form of a through hole that penetrates the catheter wall and communicates with the outside of the catheter. A sleeve is disposed on the surface. Depending on the pressure of the inflation lumen, fluid can leak out of the hole and lift the sleeve from which it can escape to the atmosphere. In this embodiment, the pressure is controlled by the elastic modulus of the sleeve material. A stiff sleeve that fits snugly into the catheter will not leak at low pressure. Also, the soft rubbery sleeve is easily lifted to release the high pressure fluid.

  The safety valve 212 of the second embodiment need not be stopped in the body of the catheter 200. Alternatively, the expansion connector 260 may itself include a pressure safety valve 212. Alternatively, a modular attachment (not shown) that includes a safety valve 212 may be attached to the expansion connector 260. Such modular valve attachments are removable and replaceable (e.g., via a conventional luer or screw connection). Thus, as long as the catheter 200 can still be used after the valve 212 has been actuated (broken), the used modular valve attachment can be replaced with a new attachment. If the catheter 200 breaks and the attachment valve remains unbroken, the reverse is also true for attachment reuse. The downstream end of the modular valve attachment (eg, molded as part of a luer connector) is removably attached to the upstream end of the expansion connector 260, and the upstream end of the modular valve attachment is a balloon expansion, usually a syringe. Connected to equipment. The upstream end of the modular valve attachment is also part of the luer connector for easy connection to standard medical equipment. In such a configuration, the safety valves 212, 312 of the present invention are completely separate from the catheters 200, 300, thus forming an improved device for attaching to any luer connector portion present in conventional catheters. Can do.

  As an alternative to the safety valve that breaks in a single use of the second embodiment, a multi-use pressure valve can be used. This third embodiment of the pressure limiting balloon catheter 300 is shown in FIG. Catheter 300 may be the same as catheter 200 of FIG. 3, except for the portion shown in FIG. Instead of having a narrowed lumen wall thickness t, the valve portion 313 extends completely into the environment (or within the drainage lumen 220, or both). However, a check valve 314 (shown only schematically in FIG. 8) is attached to the open end of the valve portion 313 and secured to the outer surface 250 of the catheter 300 to close the open end of the valve portion 313. To do. The check valve 314 can be secured directly to the outer surface 250 (eg, with an adhesive) or a connector 315 (eg, a screw cap) can secure the check valve 314 to the open end of the valve portion 313. Regardless of configuration, the check valve 314 includes a device that does not drain fluid from the lumen 230 until a given resistance R is exceeded. If a set of check valves with different resistances R is available for use by the physician, this given resistance R may be selected by the physician depending on the check valve selected for use. Similar to the second embodiment, the resistance R can be set to correspond to a desired maximum urethral pressure value. Thus, when used, fluid exits check valve 314 into the environment well before the balloon exceeds the patient's maximum urethral pressure.

  The check valve 314 can be a mechanical check valve. In addition, the check valve 314 can be a material having a tear strength corresponding to a desired set of resistances R. The material can be a liquid-tight fabric, rubber, plastic, or silicone that is different from the material comprising the catheter. The material may further be rubber, plastic, or silicone that is the same as the material comprising the catheter, but has a thickness t that is less than the thickness T of the catheter. Alternatively, the check valve 314 can be a slit valve. Various exemplary embodiments of such valves can be found in US Pat. No. 4,995,863 to Nicholas et al., Which is hereby incorporated by reference in its entirety. .

  Further, as can be appreciated, the pressure release (or safety) valve is comprised of a housing with a lumen, a ball, and a spring within the lumen, the spring pushing the ball against a defined opening, It may be a conventional pressure relief valve. When the pressure on the ball exceeds the force of the spring, the ball moves away from the defined opening and fluid moves around the ball and is discharged into the atmosphere. By controlling the tension applied to the spring, the pressure at which the valve releases the pressure can be controlled. Further, as can be appreciated, the pressure relief valve can be coupled to a luer connector, which is common for conventional urinary drainage catheters, but can be used to expand the balloon. It can be connected to a directional check valve.

  Since the safety valve 212, 312 is located at the proximal end of the catheter 200, 300, the distal end of the catheter 200, 300 is the distal end of the conventional balloon catheter 2, 3, 4, 5 Can take form. Alternatively, the distal end shown in FIG. 2 can also be used for redundant overpressure protection.

  In another exemplary embodiment of the present invention, FIGS. 9-18 show an alternative to the rubbery resilient balloon described above. In particular, the rubbery balloon described above is replaced by a thin, pre-formed fixed diameter balloon 1010. This expands without noticeable increase in diameter, substantially without pressure, from about 0.2 atmospheres (2.9 psi) to 0.5 atmospheres (7.35 psi) approximately equal to the maximum urethral pressure. Withstand pressure between. Examples of such balloon materials and thicknesses are already used in the medical field, such as those used in angioplasty. Other exemplary materials are those used in commercial (party) balloons, such as MYLAR®, or similar materials such as nylon, PTA, PTFE, polyethylene and polyurethane, for example. obtain. 9 and 13, the balloon 1010 is shown in a spherical shape. However, the balloon 1010 can be cylindrical with a flat or conical tapered end, for example.

  The expansion balloon 1010 can be formed by heating a tubular material in a mold or by heat fusing thin sheets together (eg, a party balloon has two sheets). An example of a thin balloon 1010 of the present invention that is relatively non-compliant and inflexible is formed using a blow molding process. In the blow molding process, a thermoplastic material, such as nylon, polyurethane, or polycarbonate, is extruded or formed into a hollow tubular shape (parison), followed by forming the final balloon dimensions. In a hollow mold having a shape, it is heated and pressurized, usually with air. Examples of hollow molded products are common plastic carbonated beverages or water bottle containers.

  Without limitation, one exemplary process for forming the zero pressure balloon of the present invention is described with reference to FIG. 11, and in step 1110 using standard “air mandrel” extrusion techniques. Cutting a formed piece of relatively short “parison” tube. In step 1120, one end of the tube is sealed. In step 1130, the central portion of the tube is placed in a hollow mold, leaving both ends extending outside the mold. In step 1140, the center of the tube is heated with a stream of hot air through a small hole in the center of the mold for a few seconds to soften the tube wall in the mold. In step 1150, the inside of the tube is pressurized with a fluid, such as air, to extend the tube wall to match the inside dimensions of the mold. After a short cooling period, in step 1160, additional stretching of the formed balloon is made by pulling the parison (outside), and then in step 1170, the second “ “Blow” is used to create a very thin balloon (much thinner than 0.001 inches, typically based on parison wall thickness and final balloon diameter). Then, in step 1180, the excess (uninflated) parison tube is excised from both ends, leaving the thin, relatively pliable balloon and its “legs” in the catheter as described below. It is attached.

  This exemplary process can be used, for example, to create a thin non-compliant balloon for blood vessel “angioplasty” at pressures greater than 12 atmospheres. These pressures are not essential in this application, but are evidence of the fact that very tough thin-walled balloons can be obtained from the above manufacturing process.

  The thin non-compliant zero pressure balloon of the present invention can be attached to a drainage catheter in a variety of ways. In the first exemplary mounting embodiment, reference is made to the process of FIG. 12, the slit valve of FIG. 13, and the removable balloon of FIG.

  In an exemplary embodiment, each of the distal and proximal legs of balloon 1010 manufactured according to the process of FIG. 12 is used with a standard (eg, FDA approved) bonding agent, or The two parts are attached to the distal end of the drainage catheter by heat fusing together. As an exemplary configuration of the present invention, the thin-walled non-compliant balloon is formed, for example, in such a size as to wrap around the “slit valve” shown in FIG. The thin wall of the balloon allows the balloon to be folded without a significant increase in the catheter outer diameter to facilitate catheter insertion.

  Exemplary embodiments of an intra-balloon valve 1012 according to the present invention are shown in FIGS. 13, 14 and 15. This intra-balloon valve 1012 is formed in the portion of the catheter within the balloon 1010 by cutting the wall of the drainage lumen 1120. The slit can be a single cut or multiple cuts. Some exemplary slit valves other than those shown are described in US Pat. No. 4,995,863 to Nicholas et al., All of which can be utilized in the present invention. Accordingly, the pressure to open the slit can be adjusted by adjusting the number, length and spacing of the slit (s) and the thickness of the drainage lumen wall 1122. For example, the length and orientation pressure of the slit (s) 1012 determines the pressure that it / they open the balloon inflation lumen 1130 and drain. In one particular embodiment shown in FIG. 15, the slit 1124 is cut in such a way as to penetrate a rubbery resilient wall and have a wedge-shaped cross section. Thanks to this wedge-shaped shape, the fluid in the balloon can be easily discharged under pressure. The wedge shape may increase or decrease. In the former, the edges are chamfered toward each other from the central axis of the balloon (eg, as shown in FIG. 15), and in the latter, the edges are directed toward each other, from the outside of the balloon toward the central axis. Chamfered.

  In another exemplary embodiment, a thin slit sleeve (not shown) is disposed over a portion of the drainage catheter wall 1122 in the balloon 1010 and fluidly moves the interior of the balloon 1010 to the interior of the drainage lumen 1120. The connecting through hole can be covered. Thus, the pressure in the balloon 1010 opens the slit (s) of the sleeve, thereby fluidly connecting the interior of the balloon 1010 with the drainage lumen 1120 and delivering fluid in the balloon 1010 to the drainage lumen 1120. Each of these exemplary balloon configurations completely prevents damage caused by improper expansion or premature removal.

  Alternatively, the balloon wall itself can be modified to rupture at a certain pressure, releasing the expansion medium. This weakened portion can be made, for example, by mechanical, chemical, or thermal processing. Mechanical measures can scratch the surface, thin the balloon wall at a specific part and rupture it with a pre-determined pressure, or actually slice or puncture the wall, It can be achieved by covering the area with a thin, weaker film material that tears at a predetermined pressure lower than the part. Similarly, a chemical solvent can be applied to produce the same effect as the mechanical device by causing a chemical change in the plastic molecular structure of the balloon wall, thereby weakening the desired portion of the balloon wall. It is also possible to weaken a part of the wall by heat to reorient its molecular structure (much like softening by annealing). Thus, preferential tearing of the balloon wall at a predetermined internal pressure can be accomplished in a number of ways, as illustrated but not limited to.

  A second exemplary process for attaching, but not limited to, a zero pressure balloon of the present invention to a safety catheter 1600 of the present invention that may be used with or without a slit valve is described with reference to FIGS. In step 1210, the first proximal leg 1620 of the balloon 1610 is “inverted” over the distal end of the drainage catheter shaft 1630 (as shown in FIG. Mounting step). This inverted connection can be achieved, for example, simply by using the shape of the proximal leg 1620 of the balloon 1610, or by using a separate compression device such as a rubber band, or by connecting the proximal leg 1620 to the drainage catheter shaft 1630. This is accomplished with a mechanical release that can be formed by using an adhesive that removably couples to. In the compression-only example, the proximal balloon seal can thus be used for the flexible drainage catheter shaft 1630, for example, by extending the drainage catheter shaft 1630 material (eg, silicone) to reduce its outer diameter. Formed by the force of an “inverted” relatively non-compliant proximal leg 1620 that extends over and around the distal end. The other distal leg 1640 of the balloon 1610 may then be attached at step 1220 using a bonding agent (as in the first example above) or by thermal fusing. It should be noted that the attachment method is shown and described in an inverted orientation for the proximal leg 1620 and an uninverted orientation for the distal leg 1640, but these are the only possible possibilities for each. It can be assembled in any combination of inverted and non-inverted orientations, not orientation. For example, the distal leg 1640 can be mounted in an inverted orientation not shown in FIG. 16, like the proximal leg 1620.

  To further aid in balloon attachment and catheter deflation and insertion, the outer diameter of the catheter 1600 under the balloon 1610 and the inner diameter of the distal balloon leg 1640 can be reduced relative to the outer diameter of the drainage catheter shaft 1630. . This configuration is shown in FIGS. The reduced diameter portion of the catheter 1600 is referred to herein as the distal tip portion 1650 and extends from the distal end of the drainage catheter shaft 1630 to at least the distal end of the distal balloon leg 1640. . As shown, the distal tip 5 (distal of the balloon 1610) can also have the same reduced diameter (or more greatly increased if further reduced as desired). May be good). Thus, if the outer diameter of the distal tip portion 1650 is reduced just distal to the proximal balloon seal 1620, any predetermined tensile force will extend the catheter shaft 1630, thereby causing the catheter shaft 1630 to The outer diameter is reduced at the proximal balloon seal, and the proximal balloon leg 1620 slides or peels away in the distal direction, allowing the balloon to rapidly deflate, from which all fluid is drawn. For example, released into the bladder or urethra. It is envisioned that, with similar results, the proximal balloon leg 1620 can be mounted in a “straight” position that does not flip the balloon leg 1620, if desired. However, in such a configuration, sliding of the proximal leg 1620 on the distal end of the catheter shaft 1630 can be more resistant to tensile forces on the exposed proximal end of the catheter shaft 1630. However, a slight ingress of fluid filling the balloon can be used to lubricate this connection, thus reducing drag resistance.

  In the zero pressure configuration described and referred to herein, balloons 1010, 1610 are under zero or low pressure. Thus, the expansion device (eg, syringe) need not be configured to deliver pressures much higher than the low pressure range described above. Simply because filling fluid is present in the balloon, the balloon becomes large enough to resist and prevent movement of the balloon into and out of the urethra without having high internal pressure. As such, the balloon simply does not expand if inserted improperly into the urethra. This is because there is no physical space for the balloon to expand and the expansion pressure remains below the pressure threshold that damages the urethra. If the dilator device is configured for low pressure, even the maximum delivery pressure to the balloon is insufficient to expand the balloon in the urethra, thus preventing any possibility of the balloon expanding in the urethra .

  In other cases where the balloon is properly expanded within the bladder, but the catheter is inappropriately removed from the patient without deflating the balloon, the safety device of the present invention prevents urethral rupture upon removal. . An internal balloon valve 1012 (eg, the slit valve of FIG. 13 formed through the wall of a portion of the drainage lumen 1120 disposed inside the balloon 1010, 1610), a removable proximal balloon seal 1620. Any one or both may be used to provide the safety mechanism of the present invention. In operation, when a predetermined dilation pressure is reached, the internal balloon valve 1012 opens and passes through the drainage lumen 1120 into the bladder (distal) and / or an external drain bag (proximal) not shown. Any fluid in the balloons 1010, 1610 is drained. As explained above, the point at which the pressure releases the internal balloon valve 1012 can damage the urethra when a fully expanded prior art balloon catheter is improperly removed, as described herein. It is defined to be below the pressure required to do this. In low pressure conditions where the balloons 1010, 1610 are filled with fluid (either liquid or gas), there is not enough pressure to open the inner balloon valve 1012 and allow the balloons 1010, 1610 to drain fluid. In high pressure conditions (below the pressure that damages the urethra), on the other hand, the pressure on the fluid is sufficient to open the internal balloon valve 1012, and thus fluid is quickly drained from the balloons 1010, 1610 into the drainage lumen 1120. Let me.

  In situations where the balloon 1010,1610 is in the urethra and an expansion is attempted, the pressure applied by the surrounding urethral wall on the expanding balloon 1010,1610 is increased by the internal pressure well before the balloon 1010,1610 expands. The balloon valve 1012 is opened. In this way, the balloon expansion fluid does not fill the balloons 1010, 1610, but goes directly into the drainage lumen 1120. In an alternative embodiment, the fluid used may be colored to contrast with urine (or any other fluid that is supposed to pass through the drainage lumen). In this way, when the balloons 1010, 1610 are only inserted into the urethra and an expansion is attempted, the expansion fluid immediately exits into the drainage lumen and enters an extracorporeal (not shown) drain bag. Thus, within a few seconds, the technician will know if the balloons 1010, 1610 did not enter the bladder and did not expand properly there by looking at the colored expansion fluid in the drain bag. In such situations, the technician only has to insert the catheter deeper into the urethra and try to dilate again. The absence of any further colored expansion fluid in the drain bag indicates that the correct balloon expansion has been achieved.

  In other situations where the balloon 1010, 1610 is expanded within the bladder and the catheter 100 is withdrawn from the bladder without deflating the balloon 1010, 1610, the pressure applied by the pressure urethral bladder transition 11 on the expanded balloon 1010, 1610 Causes the valve 1012 to open quickly and cause fluid to flow into the drainage lumen 1120 before the transition 11 or urethra is damaged. In such a situation, if the catheter is also provided with a removable balloon end (eg, proximal end 1620), the slit valve may be activated before or simultaneously with the removal of the removable balloon end. Open and release pressure. This drains the expansion fluid much faster than if only valve 1012 was present.

  FIGS. 16-18 illustrate an exemplary embodiment of a catheter 1600 of the present invention comprising a removable balloon 1610 that is inverted. These figures illustrate a situation where the catheter 1600 is withdrawn from the bladder without deflating the balloon 1610, as indicated by the arrow that the balloon 1610 is expanded and pulled within the bladder. Here, the distal seal 1640 of the balloon 1610 is secured to the distal tip portion 1650 of the catheter 1600 where the tip 5 has a reduced outer diameter compared to the drainage catheter shaft 1630 to provide a proximal seal. 1620 is removably attached to the drainage catheter shaft 1630 (eg, with a compression seal). The tensile force moves the drainage catheter shaft 1630 proximally out of the urethra, thereby compressing the proximal side of the expanded balloon 1610 against the urethral bladder transition 11. As the catheter shaft 1630 moves closer, the force on the proximal seal 1620 increases until the seal 1620 is free from the catheter shaft 1630, referred to herein as the separation point. FIG. 17 shows a balloon 1610 that is currently partially expanded immediately after the separation point. Since the diameter of the distal tip portion 1650 is reduced relative to the distal end of the catheter shaft 1630, it is between the inner diameter of the proximal sealing portion of the balloon 1610 and the outer diameter of the distal tip portion 1650. A gap opens. This gap allows the dilatation fluid to exit quickly from the balloon 1610 into one or both of the urethra and bladder before damage to the transition 11 or urethra occurs. Because the central portion of the balloon 1610 is still larger than the urethral opening of the transition 11, the friction and force on the balloon 1610 causes the balloon 1610 to move its own until it is completely reversed as shown in FIG. Wrap it up, ie flip it over. At this time, all of the dilating fluid is in the urethra and / or bladder.

In the exemplary embodiment of the removable proximal balloon seal 1620, a tensile force in the range of 1 to 15 pounds (4.448 to 66.72 Newtons) is free to pull the proximal balloon seal 1620. And allows the balloon 1610 to be reversed, i.e., to achieve a separation point. In another exemplary embodiment, the range of force required to achieve the separation point is between 1 and 5 pounds (4.448 to 22.24 Newtons) , particularly 1.5 to 2 pounds (6.672). To 8.896 Newton) .

  With respect to additional exemplary embodiments of a self-deflating or self-deflating balloon catheter according to the present invention, FIGS. Provided. To assist in understanding exemplary embodiments of urinary balloon catheters according to the present invention, prior art urinary catheters are used herein, both of which are applicable only to urinary catheters. It is not used herein to mean. Rather, the techniques described herein are applicable to any balloon catheter.

  FIG. 19 shows the balloon portion of a prior art catheter 1900 with the balloon in its unexpanded state. An annular lumen inner wall 1910 (red) defines a drainage lumen 1912 therein. In one circumferential longitudinal extension around the lumen inner wall 1910, the inflation lumen wall 1920 (orange) defines an inflation lumen 1922 and a balloon inflation port 1924 that is fluidly coupled to the inflation lumen 1922. In a standard urinary catheter, there is only one inflation lumen 1922 and one inflation port 1924. The views of FIGS. 19 and 20 show a cross section through the inflation lumen 1922 and the inflation port 1924. When the inflation lumen 1922 extends through the catheter 1900 to its distal end (left of FIGS. 19 and 20), the balloon cannot expand because all the expanding fluid exits at the distal end. Thus, lumen plug 1926 (black) closes inflation lumen 1922 distal to inflation port 1924 to allow balloon expansion. In this exemplary view, lumen plug 1926 begins at a location distal to inflation port 1924 at inflation lumen 1922.

  Around the inner lumen wall around the inflation port 1924 and around the inflation lumen walls 1910, 1920, there is a tube of material that forms the wall 1930 (green) inside the balloon. The tubes forming the balloon interior wall 1930 are liquid tightly sealed against their respective inner walls 1910, 1920 only at the proximal and distal ends of the tube. Therefore, a pocket is formed between them. The outer wall 1940 (yellow) covers all of the walls 1910, 1920, 1926, 1930. This is then done in a liquid tight manner, referred to herein, which means that any fluid used to inflate the balloon through inflation lumen 1922 and inflation port 1924 will pass through the fluid tight connection. This means that the catheter 1900 does not exit. FIG. 20 shows how the fluid (indicated by dashed arrows) expands the balloon. Since at least the inner wall 1930 and the outer wall 1940 of the balloon have rubber-like elasticity, the pressure exerted by the expansion fluid 2000 on these walls is, for example, as shown in FIG. Inflate. If the proximal end of the catheter 1900 (not shown) is sealed with the fluid 2000 therein (eg, with at least a portion of the luer connector shown in FIG. 3), the catheter 1900 is shown in FIG. It is kept in the shape shown.

  As explained above, the urinary catheter balloon 2010 must be inflated only when in the bladder 2020. FIG. 20 shows that the catheter 1900 has been correctly expanded with the bladder 2020 and, if necessary, then pulled proximally, the expanded balloon 2010 is placed in the urethra 2030 and the urethra 2030 is placed in the bladder. Sealing substantially from the inside of 2020. “Substantially” as used in this context is common or required in urinary catheters where most or all of the urine in the bladder 2020 is drained through the drain lumen 1912 and correctly implanted. Exceeding both urine or both means not passing around the expanded balloon 2010. Only a small amount of urine passes through the balloon 2010, advantageously smoothing the urethra 2030, but muscles in various anatomical structures in men and women seal the ends with sufficient force, It is known not to leak from the end of the urethra because it prevents a large amount of leakage.

  Although each of the walls is shown herein with a different color, the different colors do not mean that each wall must be made from a different material. These colors are used for clarity purposes only to illustrate the prior art described herein and the individual parts of the catheter of the present invention. As will be described in more detail below, most of the different colored walls are actually made of the same material in a standard urinary catheter. Some of the biocompatible materials used in standard Foley catheters include latex (natural or synthetic), silicone rubber, and styrene block copolymers, polyolefin blends, elastomer alloys (TPE-v or TPV), thermoplastics Thermoplastic elastomers (TPE) including polyurethanes, thermoplastic copolyesters, and thermoplastic polyamides are included.

  One exemplary process for making a prior art urinary catheter begins with a double lumen extrusion of latex. The double lumen thus already includes both a drainage lumen 1912 and an inflation lumen 1922. Both lumens 1912, 1922, however, are extruded without occlusions and without radial ports. Thus, to provide an inflation port 1924, a radial hole is created from the outer surface to the inflation lumen inward. Sealing of the distal end of inflation lumen 1922 is performed in subsequent steps. The tube that makes up the balloon inner wall 1930 is slid over the distal end of the multi-lumen extrudate 1910, 1920 to cover the inflation port and into the inner multi-lumen extrudate at both ends of the tube, but Except for the middle part, it is sealed liquid-tight. Since this tube can also be made of latex, it can be secured to the latex multi-lumen extrusion by any known method for liquid-tightly bonding the latex. Here, the entire semi-assembly is immersed in a liquid form of latex to create the outer wall 1940. Latex can enter at least a portion of the distal end of inflation lumen 1922, but not deep enough to plug inflation port 1924. As the latex cures, the balloon 2010 is fluid tight and is fluidly connected to the environment only through the nearest unillustrated opening of the inflation port, which is fluidly connected to the inflation lumen 1922. In this process, the inner wall 1910, the inflation lumen wall 1920, the plug 1926, the balloon inner wall 1930, and the outer wall 1940 are all made of the same latex material so that they together form a very firm and watertight balloon 2010. .

  As mentioned above, all prior art balloon catheters require surgery to remove the balloon surgically, either with a syringe similar to an expanded one, or after a doctor's diagnosis that the balloon cannot be deflated. However, it is designed to contract only when it is actively contracted by surgery.

  What have been described above are various embodiments of self-contracting or self-contracting catheters according to the present invention. Figures 21-33 illustrate a self-deflating stretch valve balloon catheter in yet another exemplary embodiment of the present invention. FIGS. 21-23 illustrate a first exemplary embodiment of a stretch valve balloon catheter 2100 according to the present invention, and FIG. 21 illustrates the balloon portion of the catheter 2100 of the present invention without the balloon being expanded. The state is shown in a state. An annular lumen inner wall 2110 (red) defines a drainage lumen 2112 therein. In one or more circumferential longitudinal extents around the lumen inner wall 2110, the inflation lumen wall 2120 (orange) includes an inflation lumen 2122 and a balloon inflation port 2124 fluidly coupled to the inflation lumen 2122. Is defined. In the catheter of the present invention, there may be more than one inflation lumen 2122 and a corresponding inflation port 2124, although only one is shown here. Accordingly, the views of FIGS. 21 and 23 show a cross section through a single inflation lumen 2122 and a single inflation port 2124. Lumen plug 2126 (black) closes inflation lumen 2122 distal to inflation port 2124. In this exemplary view, lumen plug 2126 begins at a location distal to inflation port 2124 at inflation lumen 2122. This configuration is merely exemplary and may begin at inflation port 2124 or anywhere distal thereof.

  Around the inner wall of the lumen around the inflation port 2124 and around the inflation lumen walls 2110, 2120, there is a tube of material that forms the wall 2130 (green) inside the balloon. The tubes forming the balloon interior wall 2130 are liquid tightly sealed against their respective inner walls 2110, 2120 only at the proximal and distal ends of the tube. Therefore, a pocket is formed between them. The outer wall 2140 (yellow) covers all of the walls 2110, 2120, 2126, 2130 in a liquid-tight manner. FIG. 21 shows how fluid (shown by dashed arrows) attempts to expand the balloon. Since at least the wall 2130 and the outer wall 2140 inside the balloon have rubber-like elasticity, the pressure exerted by the expansion fluid 2200 on these walls is made outward, for example, as shown in FIG. Inflate. If the proximal end of the catheter 2100 (not shown) is sealed with the fluid 2200 therein (eg, at least a portion of the luer connector shown in FIG. 3), the catheter 2100 is shown in FIG. It is kept in the shape shown.

  FIG. 22 shows that the catheter 2100 has been correctly expanded with the bladder 2020, and if necessary, then pulled proximally, the expanded balloon 2210 is placed in the urethra 2030, and the urethra 2030 is placed in the bladder. Sealing substantially from the inside of 2020.

  The stretch valve of the exemplary embodiment of FIGS. 21-23 has three different aspects. The first is a hollow stretch valve tube 2220 that is placed in the inflation lumen 2122 so as not to prevent expansion of the balloon 2210 by the fluid 2200. While the diameter of the stretch valve tube 2220 can be of any dimension that is adapted to allow unhindered fluid to flow through the inflation lumen 2122, the inner diameter of one exemplary stretch valve tube 2220 is the inflation lumen 2122. The outer diameter of the stretch valve tube 2220 is only slightly larger than the diameter of the inflation lumen 2122 (eg, the wall thickness of the tube can be between 0.05 mm and 0.2 mm). ). The proximal end of the stretch valve tube 2220 is proximal to the proximal end of the balloon inner wall 2130 in this exemplary embodiment. The distal end of the stretch valve tube 2220 is somewhere near the proximal end of the balloon inner wall 2130 and the distal end is proximal to the proximal end of the balloon inner wall 2130, the proximal end of the balloon inner wall 2130, or This may be distal to the proximal end of the balloon inner wall 2130, and the selection of this position depends on the amount of extension S required to operate the stretch valve of the catheter 2100 of the present invention, as will be described below. In FIG. 22, the distal end of the stretch valve tube 2220 is shown at the proximal end of the balloon inner wall 2130. Two ports are formed proximal to the balloon 2210. Proximal port (purple) 2150 is formed through outer wall 2140 and through inflation lumen wall 2020 and overlaps at least a portion of the proximal end of stretch valve tube 2220. Thus, a portion of the outer surface of the proximal end of the stretch valve tube 2220 at the proximal port 2150 is exposed to the environment, but the inflation lumen 2122 and the proximal port 2150 are not in fluid communication. The distal port (white) 2160 is formed through the outer wall 2140 and through the inflation lumen wall 2020 and overlaps at least a portion of the distal end of the stretch valve tube 2220. Thus, a portion of the outer surface of the distal end of the stretch valve tube 2220 at the distal port 2160 is exposed to the environment, but there is no fluid communication from the inflation lumen 2122 to the distal port 2160. To secure the stretch valve tube 2220 to the catheter 2100, the proximal port 2150 is filled with a material that secures the proximal end of the stretch valve tube 2220 to at least one of the outer wall 2140 and the inflation lumen wall 2020. . In one exemplary embodiment, the adhesive bonds the proximal end of the stretch valve tube 2220 to both the outer wall 2140 and the inflation lumen wall 2120.

In such a configuration, therefore, any proximal movement of the catheter 2100 at or near the proximal port 2150 will cause the stretch valve tube 2220 to move proximally. That is, the distal end of the stretch valve tube 2220 may slide by S in the proximal direction within the inflation lumen 2122. FIG. 23 illustrates that when the catheter 2100 is still inflated when force is applied, the proximal end of the catheter 2100 is pulled with a force that is not greater than just before the urethral bladder transition or urethra is damaged. It shows how the slide valve of the invention operates. In the exemplary embodiment of the stretch valve of FIGS. 21-23, a tensile force in the range of 1 to 15 pounds (4.448 to 66.72 Newtons) causes the stretch valve tube 2220 to slide close to S. Thus, the distal end of the stretch valve tube 2220 is positioned just proximal to the distal port 2160, ie, at the contraction point of the stretch valve shown in FIG. In another exemplary embodiment, the range of force required to achieve the contraction point is between 1 and 5 pounds (4.448 to 22.24 Newtons) , particularly 1.5 to 2 pounds (6.672). To 8.896 Newton) .

  As can be seen from FIG. 23, upon reaching the contraction point of the stretch valve, the interior of the balloon 2210 is fluidly coupled to the distal port 2160. Due to the fact that the bladder is relatively uncompressed compared to the balloon 2210 because the distal port 2160 is open to the environment (eg, inside the bladder 2020), all internal pressures are Released from 2210, the dilating fluid 2200 is drained into the bladder 2020 (indicated by dashed arrows), thereby quickly deflating the balloon 2210 (indicated by opposing solid arrows). It should be noted that the distance X (see FIG. 22) between the inflation port 2124 and the distal port 2160 directly affects the speed at which the balloon 2120 is deflated. Therefore, shortening the distance X increases the speed at which the balloon 2210 contracts. Also, the cross-sectional area of the inflation port 2124, inflation lumen 2122, and distal port 2160 directly affects the rate at which the balloon 2220 is deflated. Furthermore, any change in the direction of the fluid can hinder the rate at which the balloon is deflated. One way to speed up the contraction may be to mold the distal port 2160 into a funnel-shaped configuration (not shown) that opens outwardly from the inflation lumen 2122. Another way to speed up the contraction is to have two or more inflation lumens 2122 around the circumference of the lumen inner wall 2110, for each inflation lumen 2122, the corresponding stretch valve tube 2220, proximal port 2150, And having a set of distal ports 2160.

  Yet another possibility to rapidly deflate the expanded balloon is to drain fluid 2200 into the drain lumen 2112 rather than the bladder. This exemplary embodiment is illustrated in FIGS. 24-26. FIG. 24 shows the balloon portion of the catheter 2400 of the present invention with the balloon in its unexpanded state. An annular lumen inner wall 2410 (red) defines a drainage lumen 2412 therein. In one or more circumferential longitudinal extents around the lumen inner wall 2410, the inflation lumen wall 2420 (orange) includes an inflation lumen 2422 and a balloon inflation port 2424 fluidly coupled to the inflation lumen 2422. Is defined. In the catheter of the present invention, there may be more than one inflation lumen 2422 and a corresponding inflation port 2424, although only one is shown here. Accordingly, the views of FIGS. 24 and 26 show a cross section through a single inflation lumen 2422 and a single inflation port 2424. Lumen plug 2426 (black) closes inflation lumen 2422 distal to inflation port 2424. In this exemplary view, lumen plug 2426 begins at a location distal to inflation port 2424 at inflation lumen 2422. This configuration is merely exemplary and may begin at inflation port 2424 or anywhere distal thereof.

  Around the inner lumen wall around the inflation port 2424 and around the inflation lumen walls 2410, 2420, there is a tube of material that forms the wall 2430 (green) inside the balloon. The tubes forming the inner wall 2430 of the balloon are liquid tightly sealed against the respective inner walls 2410, 2420 only at the proximal and distal ends of the tubes. Therefore, a pocket is formed between them. The outer wall 2440 (yellow) covers all of the walls 2410, 2420, 2426, 2430 in a liquid-tight manner. FIG. 24 shows how fluid (indicated by dashed arrows) attempts to expand the balloon. Since at least the inner wall 2430 and the outer wall 2440 of the balloon have rubber-like elasticity, the pressure exerted by the expansion fluid 2200 on these walls is made outward, for example, as shown in FIG. Inflate. If the proximal end of the catheter 2400 (not shown) is sealed with the fluid 2200 therein (eg, with at least a portion of the luer connector shown in FIG. 3), the catheter 2400 is shown in FIG. It is kept in the shape shown.

  FIG. 25 shows that the catheter 2400 has been correctly dilated with the bladder 2020 and, if necessary, then pulled proximally, the expanded balloon 2510 is placed in the urethra 2030 and the urethra 2030 is placed in the bladder. Sealing substantially from the inside of 2020.

  The stretch valve of the exemplary embodiment of FIGS. 24-26 has three different aspects. The first is a hollow stretch valve tube 2520 that is placed in the inflation lumen 2422 so as not to prevent expansion of the balloon 2510 by the fluid 2200. While the diameter of the stretch valve tube 2520 can be of any dimension that allows unhindered fluid to flow through the inflation lumen 2422, the inner diameter of one exemplary stretch valve tube 2520 is the inflation lumen 2422. The outer diameter of the stretch valve tube 2520 is only slightly larger than the diameter of the inflation lumen 2122 (eg, the wall thickness of the tube can be between 0.05 mm and 0.2 mm). ). The proximal end of the stretch valve tube 2520 is disposed proximal to the proximal end of the balloon inner wall 2430 in this exemplary embodiment. The distal end of the stretch valve tube 2520 is somewhere near the proximal end of the balloon inner wall 2430 and the distal end is proximal to the proximal end of the balloon inner wall 2430, the proximal end of the balloon inner wall 2430, or This may be distal to the proximal end of the balloon inner wall 2430, and the selection of this position will depend on the amount of extension S required to operate the stretch valve of the catheter 2400 of the present invention, as will be described below. In the exemplary embodiment of FIG. 25, the distal end of stretch valve tube 2520 is shown at the proximal end of balloon inner wall 2430. Two ports are formed, one proximal to the balloon 2510 and one near the inflation port 2424. Proximal port (purple) 2450 is formed through outer wall 2440 and through inflation lumen wall 2420 and overlaps at least a portion of the proximal end of stretch valve tube 2520. Thus, a portion of the outer surface of the proximal end of the stretch valve tube 2520 at the proximal port 2450 is exposed to the environment, but the inflation lumen 2422 and the proximal port 2450 are not in fluid communication. Distal port (white) 2460 is formed through lumen inner wall 2410 somewhere proximal to inflation port 2424 and overlaps at least a portion of the distal end of stretch valve tube 2520. Thus, a portion of the outer surface of the distal end of the stretch valve tube 2520 at the distal port 2460 is exposed to the drainage lumen 2412, but the inflation lumen 2422 and the distal port 2460 are not in fluid communication. To secure the stretch valve tube 2520 to the catheter 2400, the proximal port 2450 is filled with a material that secures the proximal end of the stretch valve tube 2520 to at least one of the outer wall 2440 and the inflation lumen wall 2420. . In one exemplary embodiment, the adhesive bonds the proximal end of the stretch valve tube 2520 to both the outer wall 2440 and the inflation lumen wall 2420.

In such a configuration, therefore, any proximal movement of the catheter 2400 at or near the proximal port 2450 will cause the stretch valve tube 2520 to move proximally. That is, the distal end of the stretch valve tube 2520 may slide by S in the proximal direction within the inflation lumen 2422. FIG. 26 shows that when the catheter 2400 is still inflated when a force is applied, the proximal end of the catheter 2400 is pulled to a force that is not greater than just before the urethral bladder transition or urethra is damaged. It shows how the slide valve of the invention operates. In the exemplary embodiment of the stretch valve of FIGS. 24 to 26, a tensile force in the range of 1 to 15 pounds (4.448 to 66.72 Newtons) causes the stretch valve tube 2520 to slide close to S. Thus, the distal end of the stretch valve tube 2520 is positioned just proximal to the distal port 2460, ie, at the contraction point of the stretch valve shown in FIG. In another exemplary embodiment, the range of force required to achieve the contraction point is between 1 and 5 pounds (4.448 to 22.24 Newtons) , particularly 1.5 to 2 pounds (6.672). To 8.896 Newton) .

  As can be seen from FIG. 26, upon reaching the contraction point of the stretch valve, the interior of the balloon 2210 is fluidly coupled to the distal port 2460. The distal port 2460 is open to the drainage lumen 2412 (which is open to the interior of the bladder 2020 and the proximal drainage bag not shown) so that the bladder is compared to the balloon 2510. All internal pressure is released from the balloon 2510 due to the fact that it is not mechanically pressurized, expelling the expansion fluid 2200 into the drainage lumen 2412 (shown by the dashed arrow), thereby causing the balloon 2510 to Shrink quickly (indicated by opposing solid arrows). Again, the distance X (see FIG. 25) between the inflation port 2424 and the distal port 2460 directly affects the rate at which the balloon 2510 is deflated. Therefore, reducing the distance X increases the speed at which the balloon 2510 contracts. Also, the cross-sectional areas of inflation port 2424, inflation lumen 2422, and distal port 2460 directly affect the rate at which balloon 2120 is deflated. Furthermore, any change in the direction of the fluid can hinder the rate at which the balloon is deflated. One way to speed up the contraction may be to mold the distal port 2460 into a funnel-like configuration that opens outwardly from the inflation lumen 2422. Another way to speed up the contraction is to have two or more inflation lumens 2422 around the circumference of the lumen inner wall 2410, for each inflation lumen 2422, the corresponding stretch valve tube 2520, proximal port 2450, And having a set of distal ports 2460.

  Yet another exemplary embodiment not shown herein combines both the embodiments of FIGS. 21-23 and 24-26 to allow fluid 2200 to flow through the distal ports 2160, 2460. From both of them into the bladder 2020 and drain lumen 2112 respectively.

  Yet another possibility to rapidly deflate the expanded balloon is to drain fluid 2200 straight and directly into drain lumen 2712 without any longitudinal movement X. This exemplary embodiment is illustrated in FIGS. 27-29. FIG. 27 shows the balloon portion of the catheter 2700 of the present invention with the balloon in its unexpanded state. An annular lumen inner wall 2710 (red) defines a drainage lumen 2712 therein. In one or more circumferential longitudinal extents around the lumen inner wall 2710, the inflation lumen wall 2720 (orange) includes an inflation lumen 2722 and a balloon inflation port 2724 that is fluidly coupled to the inflation lumen 2722. Is defined. In the catheter of the present invention, there may be more than one inflation lumen 2722 and a corresponding inflation port 2724, although only one is shown here. Accordingly, the views of FIGS. 27 and 29 show a cross section through a single inflation lumen 2722 and a single inflation port 2724. Lumen plug 2726 (black) closes inflation lumen 2722 distal to inflation port 2724. In this exemplary view, lumen plug 2726 begins at a location distal to inflation port 2724 at inflation lumen 2722. This configuration is merely exemplary and may begin at inflation port 2724 or anywhere distal thereof.

  Around the inner lumen wall around the inflation port 2724 and around the inflation lumen walls 2710, 2720 there is a tube of material that forms the wall 2730 (green) inside the balloon. The tubes forming the balloon interior wall 2730 are liquid tightly sealed against their respective inner walls 2710, 2720 only at the proximal and distal ends of the tube. Therefore, a pocket is formed between them. The outer wall 2740 (yellow) covers all of the walls 2710, 2720, 2726, 2730 in a liquid-tight manner. FIG. 27 shows how fluid (indicated by dashed arrows) attempts to expand the balloon. Since at least the wall 2730 and the outer wall 2740 inside the balloon have rubber-like elasticity, the pressure exerted by the expansion fluid 2200 on these walls is made outward, for example, as shown in FIG. Inflate. If the proximal end of the catheter 2700 (not shown) is sealed with the fluid 2200 therein (eg, with at least a portion of the luer connector shown in FIG. 3), the catheter 2700 is shown in FIG. It is kept in the shape shown.

  FIG. 28 shows that the catheter 2700 has been correctly expanded with the bladder 2020 and, if necessary, then pulled proximally, the expanded balloon 2810 is placed in the urethra 2030 and the urethra 2030 is placed in the bladder. Sealing substantially from the inside of 2020.

  The stretch valve of the exemplary embodiment of FIGS. 27-29 has three different aspects. The first is a hollow stretch valve tube 2820 that is placed in the inflation lumen 2722 so as not to prevent expansion of the balloon 2810 by the fluid 2200. While the diameter of the stretch valve tube 2820 can be of any size that is adapted to allow unhindered fluid to flow through the inflation lumen 2722, the inner diameter of one exemplary stretch valve tube 2820 is the inflation lumen 2722. The outer diameter of the stretch valve tube 2820 is only slightly larger than the diameter of the inflation lumen 2722 (eg, the wall thickness of the tube can be between 0.05 mm and 0.2 mm). ). The proximal end of the stretch valve tube 2820 is proximal to the proximal end of the balloon inner wall 2730 in this exemplary embodiment. The distal end of the stretch valve tube 2820 is somewhere near the proximal end of the balloon inner wall 2730 and the distal end is proximal to the proximal end of the balloon inner wall 2730, the proximal end of the balloon inner wall 2730, or This may be distal to the proximal end of the balloon inner wall 2730, and the choice of this position will depend on the amount of extension S required to operate the stretch valve of the catheter 2700 of the present invention, as described below. In the exemplary embodiment of FIG. 28, the distal end of stretch valve tube 2820 is shown between inflation port 2724 and the proximal end of balloon inner wall 2730. Two ports are formed, one proximal to the balloon 2810 and one between the inflation port 2724 and the proximal end of the balloon inner wall 2730. Proximal port 2750 is formed through outer wall 2740 and through inflation lumen wall 2720 and overlaps at least a portion of the proximal end of stretch valve tube 2820. Thus, a portion of the outer surface of the proximal end of the stretch valve tube 2820 at the proximal port 2750 is exposed to the environment, but the inflation lumen 2722 and the proximal port 2750 are not in fluid communication. The distal port (white) 2760 is formed through both the inflation lumen wall 2720 and the distal inner wall 2710 of the proximal connection of the balloon inner wall 2730 to provide at least a portion of the distal end of the stretch valve tube 2820. And overlap. This exposes the opposing portion of the distal surface of the distal end of the stretch valve tube 2820 at the distal port 2760, ie, one is exposed inside the balloon 2810 and one is exposed to the drainage lumen 2712. However, neither the inflation lumen 2722 or the drainage lumen 2712 is in fluid communication with the distal port 2760. To secure stretch valve tube 2820 to catheter 2700, proximal port 2750 is filled with a material that secures the proximal end of stretch valve tube 2820 to at least one of outer wall 2740 and inflation lumen wall 2720. . In one exemplary embodiment, the adhesive bonds the proximal end of the stretch valve tube 2820 to both the outer wall 2740 and the inflation lumen wall 2720. In an exemplary embodiment, the adhesive may be the same material as any or all of walls 2710, 2720, 2730, 2740, or may be a different material. For example, if the outer wall 2740 is formed by immersing the inner part including the inner wall 2710 and the inflation lumen wall 2720 in a liquid bath of the same material as the double lumen extruded body, the outer wall 2740, when solidified, Integrated into both inflation lumen walls 2720 and fixedly connected to stretch valve tube 2820 via proximal port 2750.

In such a configuration, therefore, any proximal movement of the catheter 2700 at or near the proximal port 2750 will move the stretch valve tube 2820 proximally. That is, the distal end of the stretch valve tube 2820 can slide by S in the proximal direction within the inflation lumen 2722. FIG. 29 shows that when the catheter 2700 is still inflated when a force is applied, the proximal end of the catheter 2700 is pulled to a force that is not greater than just before urethral bladder transition or urethral damage occurs. It shows how the slide valve of the invention operates. In the exemplary embodiment of the stretch valve of FIGS. 27-29, a tensile force in the range of 1 to 15 pounds (4.448 to 66.72 Newtons) causes the stretch valve tube 2820 to slide close to S. Thus, the distal end of the stretch valve tube 2820 is positioned just proximal to the distal port 2760, ie, at the contraction point of the stretch valve shown in FIG. In another exemplary embodiment, the range of force required to achieve the contraction point is between 1 and 5 pounds (4.448 to 22.24 Newtons) , particularly 1.5 to 2 pounds (6.672). To 8.896 Newton) .

  As can be seen from FIG. 29, upon reaching the contraction point of the stretch valve, the interior of the balloon 2810 is fluidly coupled to both the upper and lower portions of the distal port 2760, directly and in a straight line. The distal port 2760 is open to the drainage lumen 2712 (which is open to the interior of the bladder 2020 and the proximal drainage bag not shown) so that the bladder is compared to the balloon 2810. All internal pressure is released from the balloon 2810 due to the fact that it is not mechanically pressurized, expelling the expansion fluid 2200 into the drainage lumen 2712 (represented by the dashed arrows), thereby causing the balloon 2810 to Shrink quickly (indicated by opposing solid arrows). Unlike the above embodiment, the distance X between the deflation port (the upper part of the distal port 2760) and the lower part of the distal port 2760 is zero, so the speed at which the balloon 2510 is deflated is increased further. This cannot be done (other than increasing the area of the distal port 2760). Still further, the inflation port 2724 is also fluidly coupled to the drain lumen 2712, and thus drainage of the fluid 2200 occurs via the inflation port 2724 as well. The cross-sectional area of the inflation lumen 2722 therefore affects the balloon deflation rate only slightly, if any. One way to speed up the contraction may be to mold the distal port 2760 into a funnel-shaped configuration that opens outwardly in an inward direction from the outer periphery of the catheter 2700 toward the drainage lumen 2712. Another way to speed up the contraction is to have two or more inflation lumens 2722 around the circumference of the lumen inner wall 2710, for each inflation lumen 2722, the corresponding stretch valve tube 2820, proximal port 2750, And having a set of distal ports 2760.

  FIG. 30 is a reproduction of FIG. 27 on the same page to assist in explaining FIGS. 31 and 32. 31 and 32 show the closed and open positions of the stretch valve tube 2820 of FIGS. 28 and 29, respectively. These views are counterclockwise with respect to the central longitudinal axis of the catheter 2700 viewed along the axis from the proximal end to the distal end, such that the distal port 2760 is viewed from above. It is seen in a direction rotated 90 degrees. As shown, the stretch valve tube 2820 closes the distal port 2760 without pulling the proximal end of the catheter 2700 (FIG. 31). By applying a proximal force to the proximal end of the catheter 2700, the stretch valve tube 2820 slides and no longer closes the distal port 2760, as seen in FIG.

  FIGS. 33-36 illustrate an alternative exemplary embodiment of a self-deflating stretch valve safety balloon catheter according to the present invention. With reference to these figures, the various parts of the embodiments are not described (eg, the walls inside the balloon), but the parts described above are hereby incorporated by reference into these embodiments and will not be repeated for the sake of brevity.

  FIG. 33 shows the balloon portion of the catheter 3300 of the present invention with the balloon 3302 in a partially expanded state. An annular lumen inner wall 3310 defines a drainage lumen 3312 therein. In one or more circumferential longitudinal extents around the lumen inner wall 3310, the inflation lumen wall 3320 defines an inflation lumen 3322 and a balloon inflation port 3324 that is fluidly coupled to the inflation lumen 3322. . In the catheter of the present invention, there may be more than one inflation lumen 3322 and a corresponding inflation port 3324, although only one is shown here. Accordingly, the views of FIGS. 33 and 36 show a cross section through a single inflation lumen and a single inflation port. There is no lumen plug that closes the inflation lumen 3322 distal to the inflation port 3324 as described above in an alternative embodiment. In this exemplary embodiment, the stretch valve mechanism 3330 serves to plug the inflation lumen 3322 distal to the inflation port 3324, as described in further detail below. Outer wall 3340 covers all of inner walls 3310 and 3320 in a fluid tight manner and forms the exterior of balloon 3342 but does not cover the distal end of inflation lumen 3322. Outer wall 3340 is formed in any manner described herein and will not be described in further detail here.

  A stretch valve mechanism 3330 is disposed in the inflation lumen 3322 so as not to prevent expansion of the balloon 3302 by the expansion fluid. Proximal hollow anchor portion 3332 is disposed in the inflation lumen 3320 proximal to inflation port 3324. While the diameter of the hollow anchor portion 3332 can be any dimension that is adapted to allow unhindered fluid to flow through the inflation lumen 3322, the inner diameter of one exemplary hollow anchor portion 3332 is the inflation lumen 3322. The outer diameter of the hollow anchor portion 3332 is only slightly larger than the diameter of the inflation lumen 3322 (eg, the wall thickness of the tube can be between 0.05 mm and 0.2 mm). ). The longitudinal length of the hollow anchor portion 3332 is as long as desired to be securely secured in the longitudinal direction within the inflation lumen 3322 when installed in place. The tube may provide a fixed connection only from its shape, but in addition, an adhesive may be used in any manner. One of these includes creating a proximal port as shown in the above embodiment and forming a fixed connection using a dip sheath. The distal end of the hollow anchor portion 3332 is proximal to the proximal end of the balloon 3302 in this exemplary embodiment. The distal end of the hollow anchor portion 3332 can be closer to the inflation port 3324 but not distal to the inflation port 3324 or the inflation port 3324. The ends of the hollow anchor portion 3332 can be proximal to the proximal end of the balloon 3302, the proximal end of the balloon 3302, or the distal end of the proximal end of the balloon 3302, the selection of this position being described below. Thus, it depends on the amount of extension required for the operation of the stretch valve of the catheter 3300 of the present invention. In the exemplary embodiment of FIG. 33, the stretch valve mechanism 3330 also includes an intermediate stopper wire 3334 coupled at its proximal end to the hollow anchor portion 3332 and a stopper 3336 coupled to the distal end of the stopper wire 3334. including. The stopper 3336 is slidably disposed on the inflation lumen 3322 and at the same time provides a fluid tight seal so that liquid can pass from one side of the stopper 3336 to the other in the inflation lumen 3322. It is dimensioned so that it cannot. Stopper 3336 is disposed distal to inflation port 3324. Stopper wire 3334 therefore spans inflation port 3324. This must be just distal of the inflation port 3324 because the stopper 3336 must traverse the inflation port 3324, but the hollow anchor portion can be located anywhere proximal to the inflation port 3324. The length of the stopper wire 3334 needs to be sufficient to span the inflation port 3324, but can be as long as desired, depending on where the hollow anchor portion 3332 is present and the desired amount of extension. As the catheter 3300 extends more at the proximal end and less at the distal end when pulled from the proximal end, the hollow anchor portion 3322 may become more proximal than shown in the inflation lumen 3322, and inflation may occur. It can be very close to the proximal end of lumen 3322 or even the proximal end of inflation lumen 3322.

In such a configuration, therefore, any proximal movement of the catheter 3300 at or proximal to the inflation port 3324 moves the stretch valve mechanism 3330 proximally. That is, the stopper 3336 slides in the proximal direction within the inflation lumen 3322 from the distal end of the inflation port 3324 to the proximal side of the inflation port 3324. If the catheter 3300 is still inflated when a force is applied, the proximal end of the catheter 3300 is pulled with a force that is not greater than just before the urethral bladder transition or urethra is damaged, causing the stopper 3336 to enter the inflation port 3324. When moving across, balloon 3342 fluid may be drained distally from inflation lumen 3322. In the exemplary embodiment of the stretch valve of FIG. 33, a pulling force in the range of 1 to 15 pounds (4.448 to 66.72 Newtons) will cause the stretch valve mechanism 3330 to slide closer, causing the stopper 3336 to move. Located just proximal to the inflation port 3324, ie, at the contraction point of the stretch valve shown in FIG. In another exemplary embodiment, the range of force required to achieve the contraction point is between 1 and 5 pounds (4.448 to 22.24 Newtons) , particularly 1.5 to 2 pounds (6.672). To 8.896 Newton) . As the stopper 3336 crosses the inflation port 3324, the balloon 3342 automatically deflates and dilation fluid exits the distal end of the inflation lumen 3332 open at the distal end of the catheter 3300 and enters the bladder. To be discharged.

  FIG. 34 shows the balloon portion of the catheter 3400 of the present invention with the balloon 3402 in a partially expanded state. An annular lumen inner wall 3410 defines a drainage lumen 3412 therein. In one or more circumferential longitudinal extents around the lumen inner wall 3410, the inflation lumen wall 3420 defines an inflation lumen 3422 and a balloon inflation port 3424 that is fluidly coupled to the inflation lumen 3422. . In the catheter of the present invention, there may be more than one inflation lumen 3422 and a corresponding inflation port 3424, although only one is shown here. There is no lumen plug that closes the inflation lumen 3422 distal to the inflation port 3424 as described above in an alternative embodiment. In this exemplary embodiment, the stretch valve mechanism 3430 serves to plug the inflation lumen 3422 distal to the inflation port 3424, as described in further detail below. The outer wall 3440 covers all of the inner walls 3410 and 3420 in a fluid tight manner and forms the exterior of the balloon 3442 but does not cover the distal end of the inflation lumen 3422. The outer wall 3440 is formed in any manner described herein and will not be described in further detail here.

  The stretch valve mechanism 3430 is disposed in the inflation lumen 3422 so as not to prevent expansion of the balloon 3402 by the expansion fluid. Proximal hollow anchor portion 3432 is disposed in inflation lumen 3420 proximal to inflation port 3424. While the diameter of the hollow anchor portion 3432 can be any dimension that allows unhindered fluid to flow through the inflation lumen 3422, the inner diameter of one exemplary hollow anchor portion 3432 is equal to the inflation lumen 3422. The outer diameter of the hollow anchor portion 3432 is only slightly larger than the diameter of the inflation lumen 3422 (eg, the wall thickness of the tube can be between 0.05 mm and 0.2 mm). ). The longitudinal length of the hollow anchor portion 3432 is as long as desired to be securely secured in the longitudinal direction within the inflation lumen 3422 when installed in place. The tube may provide a fixed connection only from its shape, but in addition, an adhesive may be used in any manner. One of these includes creating a proximal port as shown in the above embodiment and forming a fixed connection using a dip sheath. The distal end of the hollow anchor portion 3432 is on the proximal side of the balloon 3402 in this exemplary embodiment. The distal end of the hollow anchor portion 3432 can be closer to the inflation port 3424, but not distal to the inflation port 3424 or inflation port 3424. The ends of the hollow anchor portion 3432 can be proximal to the proximal end of the balloon 3402, proximal to the balloon 3402, or distal to the proximal end of the balloon 3402, the selection of this position being described below. Thus, it depends on the amount of extension required for the operation of the stretch valve of the catheter 3400 of the present invention. In the exemplary embodiment of FIG. 34, the stretch valve mechanism 3430 also includes an intermediate hollow stopper tube 3434 connected at its proximal end to the hollow anchor portion 3432 and a stopper 3436 connected to the distal end of the stopper tube 3434. Including. The stopper tube 3434 is simply the circumferential portion of the hollow anchor portion 3432 and is disposed on the opposite side of the inflation port 3424 so that it does not block fluid from flowing through the inflation port 3424. The stopper, on the other hand, is a solid cylinder having the same outer diameter as the hollow anchor portion 3432. The entire mechanism 3430 is slidably disposed in the inflation lumen 3422 and at the same time provides a fluid tight seal in the stopper 3436 so that liquid can be transferred from one side of the stopper 3436 to the other in the inflation lumen 3422. Dimensioned to prevent passage to the side of Stopper 3436 is disposed distal to inflation port 3424. Stopper tube 3434 therefore spans inflation port 3424. This must be just distal to the inflation port 3424 because the stopper 3436 must traverse the inflation port 3424, but the hollow anchor portion 3432 can be located anywhere proximal to the inflation port 3424. The length of the stopper tube 3434 needs to be sufficient to span the inflation port 3424, but can be as long as desired, depending on where the hollow anchor portion 3432 is present. As the catheter 3400 extends more at the proximal end and less at the distal end when pulled from the proximal end, the hollow anchor portion 3422 can be more proximal than shown in the inflation lumen 3422, and inflation can occur. It can be very close to the proximal end of lumen 3422 or even the proximal end of inflation lumen 3422.

In such a configuration, therefore, any proximal movement of the catheter 3400 at or proximal to the inflation port 3424 moves the stretch valve mechanism 3430 proximally. That is, the stopper 3436 slides proximally within the inflation lumen 3422 from the distal end of the inflation port 3424 to the proximal side of the inflation port 3424. If the catheter 3400 is still inflated when a force is applied, the proximal end of the catheter 3400 is pulled with a force that is not greater than just before the urethral bladder transition or urethra is damaged, causing the stopper 3436 to move to the inflation port 3424. When moving across, balloon 3442 fluid may be drained distally from inflation lumen 3422. In the exemplary embodiment of the stretch valve of FIG. 34, a pulling force in the range of 1 to 15 pounds (4.448 to 66.72 Newtons) causes the stretch valve mechanism 3430 to slide closer, causing the stopper 3436 to move. Located just proximal to the inflation port 3424, ie, at the contraction point of the stretch valve shown in FIG. In another exemplary embodiment, the range of force required to achieve the contraction point is between 1 and 5 pounds (4.448 to 22.24 Newtons) , particularly 1.5 to 2 pounds (6.672). To 8.896 Newton) . As the stopper 3436 crosses the inflation port 3424, the balloon 3442 automatically deflates and dilation fluid exits the distal end of the inflation lumen 3432 open at the distal end of the catheter 3400 and enters the bladder. To be discharged.

  FIG. 35 shows the balloon portion of the catheter 3500 of the present invention with the balloon 3502 partially expanded. An annular lumen inner wall 3510 defines a drainage lumen 3512 therein. In one or more circumferential longitudinal extents around the lumen inner wall 3510, the inflation lumen wall 3520 defines an inflation lumen 3522 and a balloon inflation port 3524 that is fluidly coupled to the inflation lumen 3522. . In the catheter of the present invention, there may be more than one inflation lumen 3522 and a corresponding inflation port 3524, although only one is shown here. There is no lumen plug that closes the inflation lumen 3522 distal to the inflation port 3524 as described above in an alternative embodiment. In this exemplary embodiment, the stretch valve mechanism 3530 serves to plug the inflation lumen 3522 distal to the inflation port 3524, as will be described in further detail below. Outer wall 3540 covers all of inner walls 3510 and 3520 in a fluid-tight manner and forms the exterior of balloon 3542, but does not cover the distal end of inflation lumen 3522. The outer wall 3540 is formed by any method described herein and will not be described in further detail here.

  The stretch valve mechanism 3530 is disposed in the inflation lumen 3522 so as not to prevent expansion of the balloon 3502 by the expansion fluid. Proximal hollow anchor portion 3532 is disposed in proximal inflation lumen 3520 of inflation port 3524. While the diameter of the hollow anchor portion 3532 can be any dimension that is adapted to allow unhindered fluid to flow through the inflation lumen 3522, the inner diameter of one exemplary hollow anchor portion 3532 is the inflation lumen 3522. The outer diameter of the hollow anchor portion 3532 is only slightly larger than the diameter of the inflation lumen 3522 (eg, the tube wall thickness may be between 0.05 mm and 0.2 mm). ). The longitudinal length of the hollow anchor portion 3532 is as long as desired to be securely secured in the longitudinal direction within the inflation lumen 3522 when installed in place. The tube may provide a fixed connection only from its shape, but in addition, an adhesive may be used in any manner. One of these includes creating a proximal port as shown in the above embodiment and forming a fixed connection using a dip sheath. The distal end of the hollow anchor portion 3532 is on the proximal side of the balloon 3502 in this exemplary embodiment. The distal end of the stretch valve mechanism 3530 can be closer to the inflation port 3524, but not distal to the inflation port 3524 or the inflation port 3524. The ends of the hollow anchor portion 3532 can be proximal to the proximal end of the balloon 3502, proximal to the balloon 3502, or distal to the proximal end of the balloon 3502, the selection of this position being described below. Thus, it depends on the amount of extension required for the operation of the stretch valve of the catheter 3500 of the present invention. In the exemplary embodiment of FIG. 35, the stretch valve mechanism 3530 is also coupled to an intermediate biasing device 3534 such as a spring coupled at its proximal end to the hollow anchor portion 3532 and the distal end of the biasing device 3534. A stopper 3536. A biasing device 3534 is disposed at the inflation port 3524 but does not block fluid from flowing through the inflation port 3524. The stopper 3536, on the other hand, is a solid cylinder having the same outer diameter as the hollow anchor portion 3532. The entire mechanism 3530 is slidably disposed in the inflation lumen 3522 and at the same time provides a fluid tight seal in the stopper 3536 so that liquid can be transferred from one side of the stopper 3536 to the other in the inflation lumen 3522. Dimensioned to prevent passage to the side of Stopper 3536 is disposed distal to inflation port 3524. A limiting member 3538 is provided distal to the stopper 3536 to prevent distal movement of the stopper 3536. Bias device 3534 therefore spans inflation port 3524. This must be just distal to the inflation port 3524 because the stopper 3536 must traverse the inflation port 3524, but the hollow anchor portion 3532 can be located anywhere proximal to the inflation port 3524. The length of the biasing device 3534 needs to be sufficient to span the inflation port 3524, but can be as long as desired, depending on where the hollow anchor portion 3532 is present. As the catheter 3500 extends more at the proximal end and less at the distal end when pulled from the proximal end, the hollow anchor portion 3522 can be more proximal than shown in the inflation lumen 3522, and inflation can occur. It can be very close to the proximal end of lumen 3522 or even the proximal end of inflation lumen 3522.

In such a configuration, therefore, any proximal movement of the catheter 3500 at or proximal to the inflation port 3524 moves the stretch valve mechanism 3530 proximally. That is, the stopper 3536 slides in the proximal direction within the inflation lumen 3522 from the distal side of the inflation port 3524 to the proximal side of the inflation port 3524. If the catheter 3500 is still inflated when a force is applied, the proximal end of the catheter 3500 is pulled with a force that is not greater than just before the urethral bladder transition or urethra is damaged, causing the stopper 3536 to enter the inflation port 3524. When moving across, balloon 3542 fluid may be drained distally from inflation lumen 3522. In the exemplary embodiment of the stretch valve of FIG. 35, a pulling force in the range of 1 to 15 pounds (4.448 to 66.72 Newtons) causes the stretch valve mechanism 3530 to slide closer, causing the stopper 3536 to move. Located just proximal to the inflation port 3524, ie, at the contraction point of the stretch valve shown in FIG. In another exemplary embodiment, the range of force required to achieve the contraction point is between 1 and 5 pounds (4.448 to 22.24 Newtons) , particularly 1.5 to 2 pounds (6.672). To 8.896 Newton) . As the stopper 3536 crosses the inflation port 3524, the balloon 3542 automatically deflates and the dilating fluid exits the distal end of the inflation lumen 3532 open at the distal end of the catheter 3500 and enters the bladder. To be discharged.

  FIG. 36 shows the balloon portion of the catheter 3600 of the present invention with the balloon 3602 in a partially expanded state. An annular lumen inner wall 3610 defines a drainage lumen 3612 therein. In one or more circumferential longitudinal extents around the lumen inner wall 3610, the inflation lumen wall 3620 defines an inflation lumen 3622 and a balloon inflation port 3624 that is fluidly coupled to the inflation lumen 3622. . In the catheter of the present invention, there may be more than one inflation lumen 3622 and a corresponding inflation port 3624, although only one is shown here. There is no lumen plug that closes the inflation lumen 3622 distal to the inflation port 3624 as described above in an alternative embodiment. In this exemplary embodiment, the stretch valve mechanism 3630 serves to plug the inflation lumen 3622 distal to the inflation port 3624, as described in further detail below. Outer wall 3640 fluidly covers all of inner walls 3610 and 3620 and forms the exterior of balloon 3642, but does not cover the distal end of inflation lumen 3622. The outer wall 3640 is formed by any method described herein and will not be described in further detail here.

A stretch valve mechanism 3630 is disposed in the inflation lumen 3622 so as not to prevent expansion of the balloon 3602 by the expansion fluid. A proximal anchor portion, not shown, is located in the proximal inflation lumen 3620 of the inflation port 3624. The proximal anchor portion may be of any size or shape that is adapted to allow unhindered fluid to flow through the inflation lumen 3622. The inner diameter of one exemplary hollow anchor portion is the diameter of the inflation lumen 3622. And the outer diameter is only slightly larger than the diameter of the inflation lumen 3622 (eg, the wall thickness of the tube can be between 0.07 mm and 0.7 mm). The length of the hollow anchor portion in the longitudinal direction may be as long as desired to be securely secured in the longitudinal direction within the inflation lumen 3622 when installed in place. The anchor portion is, in this exemplary embodiment, at or near the proximal end of an inflation lumen 3622 not shown. The distal end of the stretch valve mechanism 3630 is distal to the inflation port 3624. The selection of the position of the anchor portion depends on the amount of extension required to operate the stretch valve of the catheter 3600 of the present invention, as will be described below. In the exemplary embodiment of FIG. 36, the stretch valve mechanism 3630 also includes an inelastic or elastic intermediate cord 3634 that is coupled to the anchor portion at its proximal end. Stopper 3636 is coupled to the distal end of cord 3634. The cord 3634 is disposed at the inflation port 3624 but does not block fluid from flowing through the inflation port 3624. Stopper 3636, on the other hand, is a solid cylindrical body having a diameter that allows it to slide through inflation lumen 3622 when cord 3634 is pulled, but at the same time provides a fluid tight seal. Provided to prevent liquid from passing from one side of stopper 3636 to the other in inflation lumen 3622. Stopper 3636 is disposed distal to inflation port 3624. A limiting member 3638 is provided distal to the stopper 3636 to prevent distal movement of the stopper 3636. Code 3634 therefore spans inflation port 3624. This must be just distal to the inflation port 3624 because the stopper 3636 must traverse the inflation port 3624, but the anchor portion can be located anywhere proximal to the inflation port 3624. The length of the cord 3634 needs to be sufficient to span the inflation port 3624, but can be as long as desired, depending on where the anchor portion is present. As the catheter 3600 extends more at the proximal end and less at the distal end when pulled from the proximal end, the anchor portion may be very close to the proximal end of the inflation lumen 3622 or the inflation lumen. 3622 can be the proximal end. This can also be attached to one side of the luer connector to prevent fluid from flowing out of the proximal end of the inflation lumen 3622.

In such a configuration, therefore, any proximal movement of the catheter 3600 at the proximal end where the anchor portion is present also moves the stretch valve mechanism 3630 proximally. That is, the stopper 3636 slides proximally within the inflation lumen 3622 from the distal end of the inflation port 3624 to the proximal side of the inflation port 3624. If the catheter 3600 is still inflated when a force is applied, the proximal end of the catheter 3600 is pulled with a force that is not greater than just before the urethral bladder transition or urethra is damaged, causing the stopper 3636 to move to the inflation port 3624. When moving across, the fluid in balloon 3642 may be drained distally from inflation lumen 3622. In the exemplary embodiment of the stretch valve of FIG. 36, a pulling force in the range of 1 to 15 pounds (4.448 to 66.72 Newtons) causes the stretch valve mechanism 3630 to slide closer, causing the stopper 3636 to move. Located just proximal to the inflation port 3624, ie, at the contraction point of the stretch valve shown in FIG. In another exemplary embodiment, the range of force required to achieve the contraction point is between 1 and 5 pounds (4.448 to 22.24 Newtons) , particularly 1.5 to 2 pounds (6.672). To 8.896 Newton) . As the stopper 3636 crosses the inflation port 3624, the balloon 3642 automatically deflates and the dilating fluid exits the distal end of the inflation lumen 3622 open at the distal end of the catheter 3600 and enters the bladder. To be discharged.

  An alternative exemplary embodiment combines the embodiments of FIGS. 30 and 36 to connect the tube 2820 to the proximal end of the catheter.

  FIG. 37 shows the balloon portion of the catheter 3700 of the present invention with the balloon 3742 partially expanded. An annular lumen inner wall 3710 defines a drainage lumen 3712 therein. In one or more circumferential longitudinal extents around the lumen inner wall 3710, the inflation lumen wall 3720 defines an inflation lumen 3722 and a balloon inflation port 3724 that is fluidly coupled to the inflation lumen 3722. . In the catheter of the present invention, there may be more than one inflation lumen 3722 and a corresponding inflation port 3724, although only one is shown here. Lumen plug 3736 fluidly closes inflation lumen 3722 distal to inflation port 3724 so that all expansion fluid 3702 is directed into balloon 3742. Lumen plug 3736 can be plugged distally at any point or extent from inflation port 3724. Outer wall 3740 covers all of inner walls 3710 and 3720 in a fluid-tight manner and forms the exterior of balloon 3742, but does not cover the distal end of drainage lumen 3712. The outer wall 3740 is formed in any manner described herein and will not be described in further detail here.

  In this exemplary embodiment, a hollow stretch valve tube 3730 is placed in the drainage lumen 3712 so as not to impede drainage of the fluid (eg, urine) being drained. While the diameter of the stretch valve tube 3730 can be of any size that allows unhindered fluid to flow through the drainage lumen 3712, the inner diameter of one exemplary stretch valve tube 3730 is the drainage lumen 3712. The outer diameter of the stretch valve tube 3730 is only slightly larger than the diameter of the drainage lumen 3712 (eg, the wall thickness of the tube can be between 0.07 mm and 0.7 mm). ). The proximal end of stretch valve tube 3830 is in this exemplary embodiment proximal to the proximal end of contraction port 3760. The distal end of the stretch valve tube 3730 is not distal of the distal end of the balloon 3742 so that the balloon 3742 can be deflated. The distal end may be anywhere between the two ends of the balloon 3742, but is shown in an intermediate position in FIG. The distal end of the stretch valve tube 3730 is at a certain distance distal to the contraction port 3760, but the selection of this distance S is dependent on the operation of the stretch valve of the catheter 3700 of the present invention, as will be described below. Depends on the amount of extension required. In the exemplary embodiment of FIG. 37, the longitudinal length of the contraction port 3860 is shown as less than half the longitudinal length of the stretch valve tube 3730. The drainage port 3760 is formed through the lumen inner wall 3710 and the stretch valve tube 3730 is arranged to overlap at least the drainage port 3760. Thereby, a portion of the outer surface of the proximal end of the stretch valve tube 3730 closes the drainage port 3760 and prevents fluid communication through the drainage port 3760 between the balloon 3742 and the drainage lumen 3712.

  In order to secure the stretch valve tube 3730 to the catheter 3700, a proximal anchor portion 3732 is disposed proximal to the drainage lumen 3710 away from the contraction port 3760, here proximally. Proximal anchor portion 3732 can be any size or shape that is adapted to allow unhindered fluid to flow through drainage lumen 3712, and the inner diameter of hollow anchor portion 3732, one exemplary tube or ring, is Substantially the same as the diameter of the drainage lumen 3712, and the outer diameter is only slightly larger than the diameter of the drainage lumen 3712 (eg, the wall thickness of the tube may be between 0.07 mm and 0.7 mm). . The length of the long axis direction of the hollow anchor portion 3732 is as long as desired when it is installed at a predetermined position. However, the stretch valve tube 3730 is firmly fixed in the drainage lumen 3712 in the long axis direction. It can be a length that is not too short or too long. The anchor portion 3732 is at the proximal end of the balloon 3742 in this exemplary embodiment, but may be further inward (distal) of the balloon 3742 or completely proximal of the balloon 3742. Good. In the exemplary embodiment, anchor portion 3732 has a stepped distal orifice that allows the proximal end of stretch valve tube 3730 to be press fit therein, for example, for permanent connection. It can be so. In another exemplary embodiment, anchor portion 3732 is an adhesive or glue that secures the proximal end of stretch valve tube 3730 longitudinally in place within drainage lumen 3712. To do. The adhesive may be the same material as any or all of the walls 3710, 3720, 3740, or may be a different material. Exemplary non-illustrated embodiment in which a fixation port or set of fixation ports is formed through inner wall 3710 proximal to the proximal end of balloon 3742 and around the proximal end of stretch valve tube 3730 For example, when the outer wall 3740 is formed by immersing the inner part including the inner wall 3710 and the inflation lumen wall 3720 in a liquid bath of the same material as the double-lumen extruded body, when the outer wall 3740 is solidified, the outer wall 3740 It is integrated into both 3710 and the inflation lumen wall 3720 and is fixedly coupled to the stretch valve tube 3730 via a locking port (s).

In such a configuration, therefore, any proximal movement of the catheter 3700 at or proximal to the drainage port 3760 moves the stretch valve tube 3730 proximally. That is, the distal end of the stretch valve tube 3730 can slide proximally within the drainage lumen 3712. When the catheter 3700 is still inflated when a force is applied, when the proximal end of the catheter 3700 is pulled to a force that is not greater than just before the urethral bladder transition or urethra is damaged, the force is, for example, 1 To 15 pounds (4.448 to 66.72 Newtons) with a pulling force sliding the stretch valve tube 3730 proximally so that the distal end of the stretch valve tube 3730 is just proximal to the drainage port 3760 Deploy. In another exemplary embodiment, the range of force required to achieve the contraction point is between 1 and 5 pounds (4.448 to 22.24 Newtons) , particularly 1.5 to 2 pounds (6.672). To 8.896 Newton) .

  As the contraction point of the stretch valve tube 3730 begins, the interior of the balloon 3742 is fluidized directly into the drainage lumen 3712 (which is open to the interior of the bladder 2020 and the proximal drainage bag not shown). Due to the fact that the bladder is relatively uncompressed compared to the balloon 3742, all internal pressure is released from the balloon 3742 and drains the expansion fluid 3702 directly into the drainage lumen 3712. Thereby quickly deflating the balloon 3742. Since there is no intermediate structure between the balloon dilation fluid 3702 and the drainage lumen 3712, the rate at which the balloon 3742 contracts is fast. One way to speed up the contraction may be to mold the drainage port 3760 into a funnel-shaped configuration that opens outwardly from the outer wall 3740 toward the interior of the catheter 3700. Another way to speed up the contraction is to have two or more drainage ports 3760 around the circumference of the lumen inner wall 3710, or to enlarge the cross-sectional area of the drainage port 3760, or both It can be.

  FIG. 38 shows the balloon portion of the catheter 3800 of the present invention with the balloon 3842 partially expanded. An annular lumen inner wall 3810 defines a drainage lumen 3812 therein. In one or more circumferential longitudinal extents around the lumen inner wall 3810, the inflation lumen wall 3820 defines an inflation lumen 3822 and a balloon inflation port 3824 that is fluidly coupled to the inflation lumen 3822. . In the catheter of the present invention, there may be more than one inflation lumen 3822 and a corresponding inflation port 3824, although only one is shown here. Lumen plug 3836 fluidly closes inflation lumen 3822 distal to inflation port 3824 so that all expansion fluid 3802 is directed into balloon 3842. Lumen plug 3736 can plug distally at any point or extension from inflation port 3724. Outer wall 3840 fluidly covers all of inner walls 3810 and 3820 and forms the exterior of balloon 3842 but does not cover the distal end of drainage lumen 3812. The outer wall 3840 is formed by any method described herein and will not be described in further detail here.

  In this exemplary embodiment, the hollow stretch valve tube 3830 is placed in the drainage lumen 3812 so as not to impede drainage of the fluid (eg, urine) being drained. While the diameter of the stretch valve tube 3830 can be of any size that is adapted to allow unhindered fluid to flow through the drainage lumen 3812, the inner diameter of one exemplary stretch valve tube 3830 is the drainage lumen 3812. The outer diameter of the stretch valve tube 3830 is only slightly larger than the diameter of the drainage lumen 3812 (eg, the wall thickness of the tube can be between 0.07 mm and 0.7 mm). ). The proximal end of the stretch valve tube 3830 is in this exemplary embodiment proximal to the proximal end of the contraction port 3860. The distal end of the stretch valve tube 3830 is not distal of the distal end of the balloon 3842 so that the balloon 3842 can be deflated. The distal end can be anywhere between the two ends of the balloon 3842, but is shown in an intermediate position in FIG. Although the distal end of the stretch valve tube 3830 is at a certain distance distal of the contraction port 3860, the selection of this distance S is dependent on the operation of the stretch valve of the catheter 3800 of the present invention, as will be described below. Depends on the amount of extension required. In the exemplary embodiment of FIG. 38, the longitudinal length of the deflation port 3860 is shown as less than half the longitudinal length of the stretch valve tube 3830. The drainage port 3860 is formed through the lumen inner wall 3810 and the stretch valve tube 3830 is positioned to overlap at least the drainage port 3860. Thereby, a portion of the outer surface of the proximal end of the stretch valve tube 3830 closes the drainage port 3860 and prevents fluid communication through the drainage port 3860 between the balloon 3842 and the drainage lumen 3812.

  In this exemplary embodiment, compared to the embodiment of FIG. 37, a second drainage port 3862 is provided in alignment with the drainage port 3860 on the lumen inner wall 3810, and both drainage ports 3860, 3862 are inflation ports. Consistent with 3824. Thus, when the stretch valve tube 3830 moves proximally to open the drainage ports 3860, 3862, the expansion fluid 3802 from inside the balloon 3842 is drained from both the inflation port 3824 and the drainage port 3860.

  In order to secure the stretch valve tube 3830 to the catheter 3800, a proximal anchor portion 3832 is disposed in the drainage lumen 3810 away from the contraction ports 3860, 3862, here proximally. Proximal anchor portion 3832 may be any size or shape that is adapted to allow unhindered fluid to flow through drainage lumen 3812, and the inner diameter of hollow anchor portion 3832, which is one exemplary tube or ring, is Substantially equal to the diameter of the drainage lumen 3812 and the outer diameter is only slightly larger than the diameter of the drainage lumen 3812 (eg, the wall thickness of the tube may be between 0.07 mm and 0.7 mm). . The length of the long axis direction of the hollow anchor portion 3832 is as long as desired when installed in a predetermined position. However, the stretch valve tube 3830 is firmly fixed in the drainage lumen 3812 in the long axis direction. It can be a length that is not too short or too long. The anchor portion 3832 is at the proximal end of the balloon 3842 in this exemplary embodiment, but may be further inward (distal) of the balloon 3842 or completely proximal of the balloon 3842. Good. In the exemplary embodiment, anchor portion 3832 has a stepped distal orifice that allows the proximal end of stretch valve tube 3830 to be press fit therein, for example, for permanent connection. It can be so. In another exemplary embodiment, anchor portion 3832 is an adhesive or glue that anchors the proximal end of stretch valve tube 3830 longitudinally in place within drainage lumen 3812. To do. The adhesive may be the same material as any or all of the walls 3810, 3820, 3840, or may be a different material. Exemplary non-illustrated embodiment in which a fixation port or set of fixation ports is formed through inner wall 3810 proximal to the proximal end of balloon 3842 and around the proximal end of stretch valve tube 3830 Then, for example, when the outer wall 3840 is formed by immersing the inner part including the inner wall 3810 and the inflation lumen wall 3820 in a liquid bath of the same material as the double lumen extruded body, when the outer wall 3840 is solidified, the outer wall 3840 3810 and inflation lumen wall 3820 are both integrated and fixedly connected to stretch valve tube 3820 via a locking port (s).

In such a configuration, therefore, any proximal movement of the catheter 3800 at or proximal to the drainage ports 3860, 3862 will move the stretch valve tube 3830 proximally. That is, the distal end of the stretch valve tube 3830 can slide proximally within the drainage lumen 3812. When the catheter 3800 is still inflated when a force is applied, when the proximal end of the catheter 3800 is pulled to a force that is not greater than just before urethral bladder transition or urethral damage occurs, the force is, for example, 1 The stretch valve tube 3830 is slid proximally with a pulling force in the range of 15 to 15 pounds (4.448 to 66.72 Newtons) and the distal end of the stretch valve tube 3830 is in close proximity to the drainage ports 3860, 3862. To place. In another exemplary embodiment, the range of force required to achieve the contraction point is between 1 and 5 pounds (4.448 to 22.24 Newtons) , particularly 1.5 to 2 pounds (6.672). To 8.896 Newton) .

  When the contraction point of the stretch valve tube 3830 begins, the interior of the balloon 3842 is fluidized directly into the drainage lumen 3812 (which is open to the interior of the bladder 2020 and the proximal drainage bag not shown). Due to the fact that the bladder is relatively uncompressed compared to the balloon 3842, all internal pressure is released from the balloon 3842 to expel the expansion fluid 3802 directly into the drainage lumen 3812. Thereby quickly deflating the balloon 3842. Since there is no intermediate structure between the balloon dilation fluid 3802 and the drainage lumen 3812, the rate at which the balloon 3842 is deflated is fast. One way to speed up the contraction may be to mold the drainage ports 3860, 3862 into a funnel-shaped configuration that opens outwardly from the outer wall 3840 toward the interior of the catheter 3800. Another way to speed up the contraction is to have two or more drainage ports 3860 around the circumference of the lumen inner wall 3810, or to enlarge the cross-sectional area of the drainage ports 3860, 3862, or both. Could be to do.

  To describe an exemplary embodiment of a process for making a catheter according to the embodiment of FIGS. 21-23, reference is made to the flowchart of FIG.

  The catheter begins at step 3910 with a double-lumen extrusion of latex. This extrusion thus includes an annular lumen inner wall 2110 with a drainage lumen 2112 and an inflation lumen wall 2120 with an inflation lumen 2122 in a circumferential extension around one or more lumen inner walls 2110. Is defined. The double lumen thus already includes both a drainage lumen 2112 and an inflation lumen 2122. Both lumens 2112, 2122, however, are extruded without occlusions and without radial ports. Therefore, in order to provide the inflation port 2124, a radial hole needs to be created between the outer surface of the extruded body and the inflation lumen.

  In step 3912, a balloon inflation port 2124 is created to fluidly connect the extruded body environment to the inflation lumen 2122.

  Sealing of the distal end of the inflation lumen 2122 can be done by inserting or creating a plug 2126 therein at step 3914, or sealing can occur simultaneously with the creation of the outer wall 2140 described below.

  In step 3916, a balloon sleeve 2130 is placed around the inflation port 2124 and secured at both ends to the exterior of the inflation lumen wall 2120 to define a fluid-tight balloon interior 2200 therebetween. As a result, expansion of the balloon 2210 can occur through the inflation lumen 2122. For example, the tube 2130 that makes up the inner wall of the balloon is slid over the distal end of the double lumen extrusion to cover the inflation port 2124 and into the inner multi-lumen extrusion at both ends of the tube, but in the middle. Except for the part, it is liquid-tightly sealed. Since this tube can also be made of latex, it can be secured to the latex multi-lumen extrusion by any known method for liquid-tightly bonding the latex.

  In step 3918, the entire subassembly is covered with an outer wall 2140. For example, the entire subassembly is immersed in a liquid form of latex to create the outer wall 2140. In an alternative embodiment where a distal inflation lumen plug is not used, the latex can enter at least a portion of the distal end of the inflation lumen 2122, but not deep enough to plug the inflation port 2124. Can not. As the latex cures, the balloon 2210 is fluid tight and is fluidly connected to the environment only through the proximal opening of the inflation port, which is fluidly connected to the inflation lumen 2122. In this process, the inner wall 2110, the inflation lumen wall 2120, the plug 2126, the balloon wall 2130, and the outer wall 2140 are all made of the same latex material so that they together form a very firm and watertight balloon 2210. .

  The sub-process described in steps 3910 to 3920 may be omitted if desired, and may instead be accomplished by utilizing a standard Foley catheter, against which the following steps are performed.

  Here, a stretch valve is formed. Proximal port 2150 is formed through outer wall 2140 and through inflation lumen wall 2020 at step 3920. The distal port 2160 is formed through the outer wall 2140 and through the inflation lumen wall 2020 at step 3922. Then, in step 3924, the stretch valve tube 2220 is inserted through either the proximal port or the distal port 2150, 2160 such that the proximal port 2150 is at least a portion of the proximal end of the stretch valve tube 2220. Overlap and the distal port 2160 overlaps at least a portion of the distal end of the stretch valve tube 2220. This allows the two portions of the outer surface of the proximal end of the stretch valve tube 2220 at the proximal and distal ports 2150, 2160 to be exposed to the environment, but the inflation lumen 2122 and the proximal or distal port 2150. 2160 is not in fluid communication.

  In step 3926, proximal port 2150 is used to secure stretch valve tube 2220 to catheter 2100. In one exemplary embodiment, proximal port 2150 is filled with a material that secures the proximal end of stretch valve tube 2220 to at least one of outer wall 2140 and inflation lumen wall 2020. In the exemplary embodiment, the adhesive bonds the proximal end of stretch valve tube 2220 to both outer wall 2140 and inflation lumen wall 2120. In another exemplary embodiment, a portion of the subassembly is immersed in a liquid form of latex to plug the proximal port 2150 and connect the stretch valve tube 2220 to the outer wall 2140 and inflation lumen wall 2120. Secure to both. As the latex hardens, the connection at the proximal port 2150 is liquid tight and does not fluidly connect to the environment therethrough. In this process, therefore, the filled proximal port 2150, the inflation lumen wall 2120, and the outer wall 2140 are all made of the same latex material so that they together form a very firm and watertight connection. .

  In such a configuration, therefore, any proximal movement of the catheter 2100 at or near the proximal port 2150 will cause the stretch valve tube 2220 to move proximally. That is, the distal end of the stretch valve tube 2220 can slide proximally within the inflation lumen 2122.

  To describe one exemplary embodiment of a process for making a catheter according to the embodiment of FIGS. 24 to 26, reference is made to the flowchart of FIG.

  The catheter begins at step 3910 with a double-lumen extrusion of latex. This extrusion thus includes an annular lumen inner wall 2410 with a drainage lumen 2412 and an inflation lumen wall 2420 with an inflation lumen 2422 in a circumferential extension around one or more lumen inner walls 2410. Is defined. The double lumen thus already includes both a drainage lumen 2412 and an inflation lumen 2422. Both lumens 2412, 2422, however, are extruded without occlusions and without radial ports. Therefore, in order to provide the inflation port 2424, a radial hole needs to be created between the outer surface of the extruded body and the inflation lumen.

  In step 3912, a balloon inflation port 2424 is created to fluidly connect the extruded body environment to the inflation lumen 2422.

  Sealing of the distal end of the inflation lumen 2422 can be done at step 3914 by inserting or creating a plug 2426 therein, or can occur simultaneously with the creation of the outer wall 2440 described below.

  In step 3916, a balloon sleeve 2430 is placed around the inflation port 2424 and secured at both ends to the exterior of the inflation lumen wall 2420 to define a fluid-tight balloon interior 2200 therebetween. As a result, expansion of balloon 2240 can occur through inflation lumen 2422. For example, the tube 2430 that makes up the inner wall of the balloon is slid over the distal end of the double lumen extrusion to cover the inflation port 2424 and into the inner multi-lumen extrusion at both ends of the tube but in the middle. Except for the part, it is liquid-tightly sealed. Since this tube can also be made of latex, it can be secured to the latex multi-lumen extrusion by any known method for liquid-tightly bonding the latex.

  In step 3918, the entire subassembly is covered with an outer wall 2440. For example, the entire subassembly is immersed in a latex in liquid form to create the outer wall 2440. In an alternative embodiment where a distal inflation lumen plug is not used, the latex can enter at least a portion of the distal end of the inflation lumen 2422, but not deep enough to plug the inflation port 2424. Can not. As the latex cures, the balloon 2240 is fluid tight and fluidly connected to the environment only through the most proximal opening of the inflation port, which is fluidly connected to the inflation lumen 2422. In this process, the inner wall 2410, the inflation lumen wall 2420, the plug 2426, the balloon wall 2430, and the outer wall 2440 are all made of the same latex material so that they together form a very firm and watertight balloon 2240. .

  The sub-process described in steps 3910 to 3920 may be omitted if desired, and may instead be accomplished by utilizing a standard Foley catheter, against which the following steps are performed.

  Here, a stretch valve is formed. Proximal port 2450 is formed in step 3920 through outer wall 2440 and through inflation lumen wall 2020. The distal port 2460 is formed in the inflation lumen 2422 through the inner wall 2410 at step 3922. Then, in step 3924, the stretch valve tube 2520 is inserted through either the proximal port or the distal port 2450, 2460 so that the proximal port 2450 is at least a portion of the proximal end of the stretch valve tube 2520. Overlap, and the distal port 2460 overlaps at least a portion of the distal end of the stretch valve tube 2520. This causes one portion of the outer surface of the proximal end of the stretch valve tube 2520 at the proximal port 2450 to be exposed to the drain lumen 2412 and another portion of the outer surface of the distal end of the stretch valve tube 2520 at the distal port 2460. Are exposed to the environment, but there is no fluid communication from the inflation lumen 2422 to any of the proximal or distal ports 2450, 2460.

  In step 3926, proximal port 2450 is used to secure stretch valve tube 2520 to catheter 2400. In one exemplary embodiment, proximal port 2450 is filled with a material that secures the proximal end of stretch valve tube 2520 to at least one of outer wall 2440 and inflation lumen wall 2020. In the exemplary embodiment, the adhesive bonds the proximal end of stretch valve tube 2520 to both outer wall 2440 and inflation lumen wall 2420. In another exemplary embodiment, a portion of the subassembly is immersed in a liquid form of latex to plug the proximal port 2450 and connect the stretch valve tube 2520 to the outer wall 2440 and inflation lumen wall 2420. Secure to both. As the latex hardens, the connection at the proximal port 2450 is liquid tight and does not fluidly connect to the environment therethrough. In this process, therefore, the filled proximal port 2450, the inflation lumen wall 2420, and the outer wall 2440 are all made of the same latex material so that they together form a very firm and watertight connection. .

  In such a configuration, therefore, any proximal movement of the catheter 2400 at or near the proximal port 2450 will cause the stretch valve tube 2520 to move proximally. That is, the distal end of the stretch valve tube 2520 can slide proximally within the inflation lumen 2422.

  To describe an exemplary embodiment of a process for making a catheter according to the embodiment of FIGS. 27-29, reference is made to the flowchart of FIG.

  The catheter begins at step 4010 with a double-lumen extrusion of latex. This extrusion thus includes an annular lumen inner wall 2710 with a drainage lumen 2712 and an inflation lumen wall 2720 with an inflation lumen 2722 in a circumferential longitudinal extension around one or more lumen inner walls 2710. Is defined. The double lumen thus already includes both a drainage lumen 2712 and an inflation lumen 2722. Both lumens 2712, 2722, however, are extruded without occlusions and without radial ports. Therefore, in order to provide the inflation port 2724, a radial hole needs to be created between the outer surface of the extruded body and the inflation lumen.

  In step 4012, a balloon inflation port 2724 is created to fluidly connect the extruded body environment to the inflation lumen 2722.

  Unlike the other exemplary embodiments described, the distal port 2760 is created in step 4014 before, after, or simultaneously with the balloon inflation port 2724. Distal port 2760 connects the environment to the interior of drain lumen 2712. In the exemplary embodiment, distal port 2760 is proximal to balloon inflation port 2724.

  Sealing of the distal end of the inflation lumen 2722 can be done at step 4016 by inserting or creating a plug 2726 therein, or sealing can occur simultaneously with the creation of the outer wall 2740 described below.

  At step 4018, a balloon sleeve 2730 is placed around the inflation port 2724 and distal port 2760 and secured at both ends to the exterior of the inflation lumen wall 2720 to define a fluid-tight balloon interior 2200 therebetween. As a result, expansion of the balloon 2210 can occur through the inflation lumen 2722. For example, the tube 2730 that makes up the inner wall of the balloon is slid over the distal end of the double lumen extrusion to cover the inflation port 2724 and into the inner multi-lumen extrusion at both ends of the tube, but in the middle. Except for the part, it is liquid-tightly sealed. Since this tube can also be made of latex, it can be secured to the latex multi-lumen extrusion by any known method for liquid-tightly bonding the latex.

  Here, the stretch valve is completed. Proximal port 2750 is formed through inflation lumen wall 2020 at step 4020. Then, in step 4022, the stretch valve tube 2820 is inserted through either the proximal port or the distal port 2750, 2760 so that the proximal port 2750 is at least a portion of the proximal end of the stretch valve tube 2820. Overlap and the distal port 2760 overlaps at least a portion of the distal end of the stretch valve tube 2820. This allows the two portions of the outer surface of the proximal end of the stretch valve tube 2820 at the proximal and distal ports 2750, 2760 to be exposed to the environment, but the inflation lumen 2722 and the proximal or distal port 2750. , 2760 are not in fluid communication. Alternatively, step 4022 can occur before 4018 to insert the stretch valve tube 2820 before the balloon sleeve 2730 is deployed and secured. In such a case, creation of proximal port 2750 can occur before, after, or simultaneously with creation of distal port 2760 and balloon inflation port 2724, and in this embodiment, all three ports 2724, 2750, 2760 are simultaneously Can be created.

  In step 4024, the entire subassembly is covered with an outer wall 2740. For example, the entire semi-assembly is immersed in a liquid form of latex to create the outer wall 2740. In an alternative embodiment where a distal inflation lumen plug is not used, the latex can enter at least a portion of the distal end of the inflation lumen 2722, but not deep enough to plug the inflation port 2724. Can not. As the latex cures, the balloon 2210 is fluid tight and is fluidly connected to the environment only through the proximal opening of the inflation port, which is fluidly connected to the inflation lumen 2722. In this process, the inner wall 2710, the inflation lumen wall 2720, the plug 2726, the balloon wall 2730, and the outer wall 2740 are all made of the same latex material so that they together form a very firm and watertight balloon 2210. .

  In the previous embodiment, the proximal port 2750 passes through the outer wall 2740. In this exemplary embodiment, however, this is not necessary. Here, the proximal port 2750 may be filled with the material of the outer wall 2740 itself to secure the proximal end of the stretch valve tube 2820 to at least one of the outer wall 2740 and the inflation lumen wall 2020. As the latex cures, the junction at the proximal port 2750 is liquid tight and does not fluidly connect to the environment therethrough. In this process, therefore, the filled proximal port 2750, the inflation lumen wall 2720, and the outer wall 2740 are all made of the same latex material so that they together form a very firm and watertight connection. . In an alternative exemplary embodiment, an adhesive may be used to join the proximal end of the stretch valve tube 2820 to the inflation lumen wall 2720.

  In such a configuration, therefore, any proximal movement of the catheter 2700 at or near the proximal port 2750 will move the stretch valve tube 2820 proximally. That is, the distal end of the stretch valve tube 2820 can slide proximally within the inflation lumen 2722.

  To describe an exemplary embodiment of a process for making a catheter according to the embodiment of FIGS. 37 and 38, reference is made to the flowchart of FIG.

  The catheter begins at step 4110 with a double lumen extrusion of latex. This extrusion therefore includes an inflation lumen 3722, an annular lumen inner wall 3710, 3810 with a drainage lumen 3712, 3812 and a circumferential longitudinal extension around one or more lumen inner walls 3710, 3810. Inflation lumen walls 3720, 3820 comprising 3822 are defined. The double lumen thus already includes both drainage lumens 2712, 2812 and inflation lumens 2722, 2822. Both lumens 2712, 2722, 2812, 2822, however, are extruded without occlusions and without radial ports. Therefore, in order to provide the inflation ports 3724, 3824, a radial hole needs to be created between the outer surface of the extruded body and the inflation lumen.

  In step 4112, balloon inflation ports 3724, 3824 are created to fluidly connect the extrusion environment to the inflation lumens 3722, 3822.

  Unlike the other exemplary embodiments described, for the embodiment of FIG. 37, the deflation port 3760 is created in step 4114 before, after, or simultaneously with the balloon inflation port 3724. The deflation port 3760 connects the interior of the balloon 3742 to the interior of the drain lumen 3712. In the exemplary embodiment, the deflation port 3760 is proximal to the balloon inflation port 3724, but may be at the balloon inflation port 3724 or distal to the balloon inflation port 3724.

  Unlike the other exemplary embodiments described, for the embodiment of FIG. 38, drainage ports 3860 and 3862 are created in step 4114 before, after, or simultaneously with the balloon inflation port 3824. Drainage port 3860 connects the interior of balloon 3842 to the interior of drain lumen 2712, and drainage port 3862 connects the interior of inflation lumen 3822 to the interior of drain lumen 2712. In the exemplary embodiment, drainage ports 3860, 3862 are aligned with balloon inflation port 3824, which may be distal or proximal. When aligned, a single through-hole is created through the entire catheter to connect both inflation and drainage channels 3712, 3722, 3812, 3822 and both catheter walls 3710, 3720, 3810, 3820. Can penetrate. Alternatively, the drainage ports 3860, 3862 can be spaced apart from each other with either one aligned with the inflation port 3824 or neither aligned.

  In step 4116, the fixing through-holes 3732 and 3832 are created without passing through the inflation lumen walls 3720 and 3820 though passing through both surfaces of the outer wall 3810. The fixing through holes 3732 and 3832 create a means for fixing the stretch valve pipes 3730 and 3830 inside the drainage lumens 3712 and 3812. The securing through holes 3732, 3832 can be located anywhere proximal to the drainage ports 3760, 3860, 3862. The fixing through holes 3732 and 3832 need not be circumferentially aligned with the inflation ports 3724 and 3824 if desired, but the fixing through holes 3732 and 3832 of FIGS. 37 and 38 are aligned therewith. Is shown. In the exemplary embodiment, the fixation through-holes 3732, 3832 are still inside the proximal end of the balloon 3842, but can also be further proximal to the balloon 3842 to any length.

  Sealing the distal end of the inflation lumens 3722, 3822 may be performed at step 4118 by inserting or creating plugs 3736, 3836 therein, or prior to forming the fixation port or at step 4124 below. Sealing can occur immediately before or simultaneously with the creation of the outer walls 3740, 3840.

  In step 4120, the stretch valve tubes 3730, 3830 are inserted into the drainage lumens 3712, 3812, and the stretch valve tubes 3730, 3830 pass through all the drainage ports 3760, 3860, 3862 and all the fixing through holes 3732, 3832. Aligned to cover. The distal ends of the stretch valve tubes 3730, 3830 are positioned at a desired distal distance S for stretch valve operation. For example, the distance can be up to 1 mm, up to 2 mm, up to 3 mm and up to 1 or 2 cm. The distance S can also depend on the amount of extension at the proximal end of the catheter, since the displacement of the stretch valve tube is proportional to the catheter elongation. For example, if the catheter is 500 mm long and pulled 20%, it will be 600 mm long (100 mm elongation). A 10 mm or larger stretch valve tube made of a hard material such as metal (eg, stainless steel, titanium, etc.), polycarbonate, polyimide, polyamide, polyurethane (Shore hardness 55D-75D), placed near the balloon of the catheter. Is glued at its proximal end to the inside of the inflation lumen or drainage lumen. When the catheter is extended 20%, the distal tip of the 10 mm stretch valve moves 2 mm in the proximal direction. Thus, if the drainage port (s) is placed 2 mm proximal to the distal end of the stretch valve tube (where S = 2 mm), it was sealed by a stretch valve tube that was stretched about 20% Will remain. However, if the catheter is pulled slightly more than 20% (or 2 mm), the drainage port is opened and the expansion fluid in the balloon is released from the drainage port. Since catheters vary from manufacturer to manufacturer, elongation calibration for the force required to extend the catheter can be made for each different type of catheter. This force is defined in engineering terms as the elastic modulus of the catheter and is a function of the elastic modulus of the material and the effective wall thickness of the catheter. When subjected to the same force, low modulus materials and catheters extend more than high modulus materials and catheters. Exemplary catheters are made from latex rubber or silicone rubber. Silicone rubber generally has a higher modulus of elasticity than latex and therefore requires more force to extend the catheter sufficiently to exert pressure in the balloon. Those skilled in the art will appreciate that different stretch valve lengths may be provided to release the balloon pressure in response to pulling forces applied to different catheters made of different materials and having different wall thicknesses. Thus, although stretch valve tube distances are given, these are exemplary and may vary for different catheters having different materials / wall thicknesses. As such, these exemplary distances for actuating a stretch valve tube apply to all embodiments described herein, but are not limited to such.

  If the fixing through-holes 3732, 3832 are in the expansion due to the expansion of the balloon sleeve (as shown), an adhesive is used in the fixing through-holes 3732, 3832 before the balloon sleeve is attached. Thus, the proximal ends of the stretch valve tubes 3730, 3830 can be fixed. Same as fixing the proximal end of the balloon sleeve if the fixing through-holes 3732 and 3832 are in the extent of the balloon sleeve but overlap only at the fixed proximal end of the balloon sleeve (not shown) Adhesive may be used in the fixation through holes 3732, 3832 where the proximal ends of the stretch valve tubes 3730, 3830 may be fixed. Finally, if the fixation through-holes 3732, 3832 are on the proximal side outside the balloon sleeve spread, the same material that makes the adhesive or outer wall 3740, 3840 (see below) is the fixation through-hole 3732, 3832. Used to secure the proximal end of the stretch valve tube 3730, 3830.

  In step 4122, the balloon sleeve is placed around the inflation ports 3724, 3824 and the fixation through holes 3732, 3832 (if the fixation through holes 3732, 3832 are within the balloon sleeve's extent), and the balloon sleeve is , At both ends, secured to the outside of the inner wall and inflation lumen walls 3710, 3720, 3810, 3820 to define a liquid tight balloon interior therebetween. As a result, expansion of balloons 3742, 3842 may occur through inflation lumens 3722, 3822. For example, the balloon sleeve that makes up the inner walls of the balloons 3742, 3842 is slid over the distal end of the double lumen extrudate to cover at least the inflation ports 3724, 3824 and into the inner multi-lumen extrudate. It is sealed fluid tight at both ends of the balloon sleeve, but at the middle. Since the balloon sleeve can also be made of latex, it can be secured to the latex multi-lumen extrudate in any known manner that adheres the latex in a liquid-tight manner.

  In step 4124, the entire subassembly is covered with outer walls 3740, 3840. For example, the entire subassembly is immersed in a liquid form of latex to create outer walls 3740, 3840. In an alternative embodiment where a distal inflation lumen plug 3736, 3836 is not used, the latex can enter at least a portion of the distal end of the inflation lumen 3722, 3822, but plugs the inflation ports 3724, 3824. I can't go in as deeply as I can. As the latex cures, the balloons 3742, 3842 are fluid tight and are fluidly connected to the environment only through the proximal opening of the inflation port, which is fluidly connected to the inflation lumens 3722, 3822. In this process, the inner walls 3710, 3810, inflation lumen walls 3720, 3820, plugs 3736, 3836, balloon walls, and outer walls 3740, 3840 are all made of the same latex material, so they are united and very solid Watertight balloons 3742, 3842 are formed.

  In such a configuration, therefore, any proximal movement of the catheter 3700, 3800 at or proximal to the proximal anchor portion 3732, 3832 moves the stretch valve tube 3730, 3830 proximally. That is, the distal ends of the stretch valve tubes 3730, 3830 can slide proximally within the inflation lumens 3722, 3822.

  In the exemplary embodiment, the steps outlined above need not be performed in the order described or illustrated. Any of these steps may exist in any order to create a catheter according to various exemplary embodiments.

  42 and 43 illustrate the balloon portion of another exemplary embodiment of the catheters 4200, 4300 of the present invention, with the balloon 3842 also in a partially expanded state. In these exemplary embodiments, most of the features are the same as the catheter 3800 shown in FIG. 38, as well as other exemplary embodiments of safety catheters described herein. 42 and 43 differ in the manner in which the stretch valve operates, and thus similar features use the same reference numbers as in FIG. Different features, however, use new reference numbers. As such, descriptions of similar features are not repeated below, but instead are incorporated herein by reference from the above-described exemplary embodiments.

  In catheters 4200, 4300, annular lumen inner walls 4210, 4310 define drainage lumens 4212, 4312 therein. In this exemplary embodiment, the hollow stretch valve tube 3830 is disposed in the drainage lumens 4212, 4312 so as not to impede drainage of the fluid (eg, urine) being drained. While the diameter of the stretch valve tube 3830 can be any dimension that allows unhindered fluid to flow through the drainage lumens 4212, 4312, the inner diameter of one exemplary stretch valve tube 3830 is the drainage Substantially equal to the diameter of the lumens 4212, 4312, the outer diameter of the stretch valve tube 3830 is only slightly larger than the diameter of the drainage lumens 4212, 4312 (eg, the wall thickness of the tube is 0.07 mm to 0.7 mm). Can be between). (In any embodiment of the stretch valve tube described herein, the outer diameter is equal to or less than the diameter of the drainage lumen.)

  The proximal end of the stretch valve tube 3830 is in this exemplary embodiment proximal to the proximal end of the contraction port 3860. The distal end of the stretch valve tube 3830 is not distal of the distal end of the balloon 3842 so that the balloon 3842 can be deflated. The distal end may be anywhere between the two ends of the balloon 3842, but is shown in an intermediate position in FIGS. The distal end of the stretch valve tube 3830 is at a certain distance S distal to the contraction port 3860, but the selection of this distance S will be described below with the stretch valves of the catheters 4200, 4300 of the present invention. Depends on the amount of extension required for operation.

  In the exemplary embodiment of FIGS. 38, 42 and 43, the longitudinal length of the contraction port 3860 is shown as less than half the longitudinal length of the stretch valve tube 3830. The drainage port 3860 is formed through the lumen inner wall 3810 and the stretch valve tube 3830 is positioned to overlap at least the drainage port 3860. Thus, a portion of the outer surface of the proximal end of the stretch valve tube 3830 closes the drainage port 3860 and prevents fluid communication through the drainage port 3860 from the balloon 3842 to the drainage lumens 4212, 4312. A second drainage port 3862 is provided in the lumen inner wall 3810 in alignment with the drainage port 3860, and both drainage ports 3860, 3862 are in alignment with the inflation port 3824. Thus, when the stretch valve tube 3830 moves proximally to open the drainage ports 3860, 3862, the expansion fluid 3802 from inside the balloon 3842 is drained from both the inflation port 3824 and the drainage port 3860.

  To secure the stretch valve tube 3830 to the catheters 4200, 4300, proximal anchor portions 4232, 4332 move away from the constriction ports 3860, 3862 to the drainage lumen 4212, here proximally, in FIG. In FIG. 43, they are arranged at a distance F. The distance shown is not the only dimension for the stretch valve tube 3830, and may be short or long, and if so, extends far proximally within the drainage lumens 4212, 4312 beyond that shown in FIG. . Proximal anchor portion 3832 may be of any size or shape that is adapted to allow unhindered fluid to flow through drainage lumens 4212, 4312 of hollow anchor portion 3832, which is one exemplary tube or ring. The inner diameter is substantially equal to the diameter of the drainage lumen 4212 and the outer diameter is only slightly larger than the diameter of the drainage lumen 4212 (eg, the wall thickness of the tube is between 0.07 mm and 0.7 mm). obtain). Proximal anchor portion 3832 can be integral or coupled to stretch valve tube 3830, can be barbed or other mechanical anchoring device. The longitudinal length of the anchor portion 3832 is as long as desired when installed in place, but the proximal end of the stretch valve tube 3830 is firmly secured in the drainage lumen 4212 in the longitudinal direction. It can be long enough to fix. Anchor portion 3832 is in this exemplary embodiment at the proximal end of balloon 3842, as shown in FIG. 42, but may be further inside balloon 3842 (ie, distal with respect to FIG. 42). However, it may be completely proximal to the balloon 3842, as shown in FIG. The more proximal the proximal anchor portion 3832 is coupled within the drainage lumens 4212, 4312, the greater the distance at which the extending material is placed between the anchor portion 3832 and the drainage ports 3860, 3862. , Thereby enhancing the ability of the safety catheter to extend and actuate the stretch valve.

In such a configuration, therefore, any proximal movement of the catheter 4200, 4300 at or proximal to the drainage port 3860, 3862 will move the stretch valve tube 3830 proximally. That is, the distal end of the stretch valve tube 3830 can slide proximally within the drainage lumen 4212. When the catheter 4200, 4300 is still inflated when a force is applied, the force is pulled when the proximal end of the catheter 4200, 4300 is pulled to a force that is not greater than just before urethral bladder transition or urethral damage occurs. For example, with a pulling force in the range of 1 to 15 pounds (4.448 to 66.72 Newtons) , the distal end of the stretch valve tube 3830 is slid proximally and moved to drainage ports 3860, 3862. Release at the contraction point. In another exemplary embodiment, the range of force required to achieve the contraction point is between 1 and 5 pounds (4.448 to 22.24 Newtons) , particularly 1.5 to 2 pounds (6.672). To 8.896 Newton) .

  When the contraction point of the stretch valve tube 3830 begins, the interior of the balloon 3842 is directly into the drainage lumens 4212, 4312 (which is open to the interior of the bladder 2020 and the proximal drainage bag not shown). Due to the fact that it is fluidly coupled and the bladder is relatively uncompressed compared to the balloon 3842, all internal pressure is released from the balloon 3842 and the expansion fluid 3802 directly into the drainage lumens 4212, 4312. The balloon 3842 is quickly deflated.

  If the proximal end of the catheter 4200, 4300 is pulled to a force sufficient to reach the desired point of contraction (and not greater than just before the injury occurs), the distal end of the stretch valve tube 3830 will frictionally There is a possibility of not sliding or sliding. In order to prevent such a situation from occurring, it is desirable to enhance the stretchability of the lumen inner wall 4210 distal to the anchor portion 3832, particularly at the extent E between the drainage ports 3860, 3862 and the anchor portion 3832. Because the catheter material described herein is inherently stretchable, there are various ways to extend the spread E more than other portions of the catheter, particularly the proximal portion of the anchor portion 3832. . One way to increase stretch is to score the outside or inside of the material containing the spread E with small cuts, notches, scratches, or other intentionally formed defects. Another way to make the spread E more elastic than at least the proximal portion of the anchor portion 3832 is to grind the exterior or interior of the spread E. A further method for making the spread E highly elastic is to chemically treat the material containing the spread E. Yet another way to make the spread E highly elastic is to treat the material containing the spread E with a local temperature change, such as heating the spread E.

  A completely different method is to use different materials for the catheters 4200, 4300. In an exemplary embodiment, at least a portion of the spread E is replaced with another rubbery elastic material that is different from the rest of the catheter, and the other rubbery elastic material is: More resilient than at least a portion of the catheter proximal to anchor portion 3832. In another exemplary embodiment, the proximal portion of anchor portion 3832 is made from a rubbery resilient material that is less resilient than the spread E.

  FIG. 43 shows a stretch valve tube 4330 that is significantly longer than the other stretch valve tubes and attached to the lumen inner wall 4310 by anchors 4332 even more proximal than the other stretch valve tubes. By lengthening the stretch valve tube 4330, the spread E is increased, thereby facilitating the extension of the portion just distal of the anchor portion 3832 to ensure actuation of the stretch valve. Any of the exemplary embodiments of the stretch valve tube may have a different length than that shown or described, or both.

  Exemplary embodiments 4200, 4300 are shown herein with reference to FIG. 38, but are not limited to each of the other exemplary embodiments described herein. Can also be applied. Furthermore, features that enhance stretchability may be added to the outer wall instead of or in addition to the lumen inner wall. If the manufacture of any of the catheters described herein includes extension reinforcements 4270, 4370, a separate manufacturing step is required. Therefore, for example, the extension reinforcement creation step is added anywhere after step 3910 in the flowchart of FIG. 39, anywhere after step 4010 in the flowchart of FIG. 40, and anywhere after step 4110 in the flowchart of FIG. Is done.

  Alternative exemplary embodiments combine various features of the embodiments described herein. For example, FIGS. 44-47 illustrate other exemplary embodiments of the stretch valve tube described above. Where some features have already been mentioned, similar reference numbers are used and the description will not be repeated.

  In contrast to the uninterrupted tube, with respect to FIGS. 44 and 45, the stretch valve tube 4430 of the catheter 4500 of the present invention comprises a proximal tubular portion 4432, a distal tubular portion 4434, and an intermediate connection 4436. Have. FIG. 45 shows the balloon portion of the catheter 4500 of the present invention with the balloon 3842 partially expanded. An annular lumen inner wall 3810 defines a drainage lumen 3812 therein. In one or more circumferential longitudinal extents around the lumen inner wall 3810, the inflation lumen wall 3820 defines an inflation lumen 3822 and a balloon inflation port 3824 that is fluidly coupled to the inflation lumen 3822. . In the catheter 4500 of the present invention, there may be more than one inflation lumen 3822 and corresponding inflation port 3824, although only one is shown here. Lumen plug 3836 fluidly closes inflation lumen 3822 distal to inflation port 3824 so that all expansion fluid 3802 is directed into balloon 3842. Lumen plug 3736 can plug distally at any point or extension from inflation port 3724. Outer wall 3840 fluidly covers all of inner walls 3810 and 3820 and forms the exterior of balloon 3842 but does not cover the distal end of drainage lumen 3812. The outer wall 3840 is formed by any method described herein and will not be described in further detail here.

  In this exemplary embodiment, the stretch valve tube 4430 is placed in the drainage lumen 3812 so as not to impede drainage of the drained fluid (eg, urine). While the diameter of the stretch valve tube 4430 can be of any dimension that is adapted to allow unhindered fluid to flow through the drainage lumen 3812, the inner diameter of one exemplary stretch valve tube 4430 is the drainage lumen 3812. The outer diameter of the stretch valve tube 4430 is only slightly larger than the diameter of the drainage lumen 3812 (eg, the wall thickness of the tube can be between 0.07 mm and 0.7 mm). ). The proximal tubular portion 4432 of the stretch valve tube 4430 is proximal to the proximal end of the contraction port 3860 in this exemplary embodiment. The distal tubular portion 4434 of the stretch valve tube 4430 is not distal of the distal end of the balloon 3842 so that the balloon 3842 can be deflated. The distal end may be anywhere between the two ends of the balloon 3842, but is shown in an intermediate position in FIG. The distal tubular portion 4434 of the stretch valve tube 4430 covers the contraction port 3860 in the longitudinal direction when the valve is in a steady state or inactive state. The distance of overlap S distal of the deflation port 3860 depends on the amount of extension required to actuate the stretch valve of the catheter 4500 of the present invention, as will be described below.

  In order to secure the stretch valve tube 4430 to the catheter 4500, a proximal anchor portion 3832 is disposed on the drainage lumen 3810 away from the contraction ports 3860, 3862, here proximally. Proximal anchor portion 3832 may be any size or shape that is adapted to allow unhindered fluid to flow through drainage lumen 3812, and the inner diameter of hollow anchor portion 3832, which is one exemplary tube or ring, is Substantially equal to the diameter of the drainage lumen 3812 and the outer diameter is only slightly larger than the diameter of the drainage lumen 3812 (eg, the wall thickness of the tube may be between 0.07 mm and 0.7 mm). . Proximal anchor portion 3832 can be integral or coupled to stretch valve tube 4430, can be barbed or other mechanical fixation device. The length of the long axis direction of the hollow anchor portion 3832 is as long as desired when installed in a predetermined position, however, the stretch valve tube 4430 is firmly fixed in the drainage lumen 3812 in the long axis direction. It can be a length that is not too short or too long. The anchor portion 3832 is at the proximal end of the balloon 3842 in this exemplary embodiment, but may be further inside (distal) of the balloon 3842 or fully proximal of the balloon 3842 as shown. It may be. In the exemplary embodiment, anchor portion 3832 has a stepped distal orifice that allows the proximal end of stretch valve tube 4430 to be press fit therein, for example, for permanent connection. It can be so. In another exemplary embodiment, anchor portion 3832 is an adhesive or glue that anchors the proximal end of stretch valve tube 4430 in a longitudinal direction in place within drainage lumen 3812. To do. The adhesive may be the same material as any or all of the walls 3810, 3820, 3840, or may be a different material. Exemplary non-illustrated embodiment in which a fixation port or set of fixation ports is formed through inner wall 3810 proximal to the proximal end of balloon 3842 and around the proximal end of stretch valve tube 4430 Then, for example, when the outer wall 3840 is formed by immersing the inner part including the inner wall 3810 and the inflation lumen wall 3820 in a liquid bath of the same material as the double lumen extruded body, when the outer wall 3840 is solidified, the outer wall 3840 3810 and inflation lumen wall 3820 are both integrated and fixedly connected to stretch valve tube 3820 via a locking port (s).

In such a configuration, therefore, any proximal movement of the catheter 4500 at or proximal to the contraction ports 3860, 3862 will move the stretch valve tube 4430 proximally. That is, the distal end of the stretch valve tube 4430 can slide proximally within the drainage lumen 3812. When the catheter 4500 is still inflated when a force is applied, when the proximal end of the catheter 4500 is pulled to a force that is not greater than just before urethral bladder transition or urethral damage occurs, the force is, for example, 1 The stretch valve tube 4430 is slid proximally with a pulling force in the range of 15 to 15 pounds (4.448 to 66.72 Newtons) so that the distal end of the stretch valve tube 4430 is in close proximity to the contraction ports 3860, 3862. To place. In another exemplary embodiment, the range of force required to achieve the contraction point is between 1 and 5 pounds (4.448 to 22.24 Newtons) , particularly 1.5 to 2 pounds (6.672). To 8.896 Newton) .

  When the contraction point of the stretch valve tube 4430 begins, the interior of the balloon 3842 is fluidized directly into the drainage lumen 3812 (which is open to the interior of the bladder 2020 and the proximal drainage bag not shown). Due to the fact that the bladder is relatively uncompressed compared to the balloon 3842, all internal pressure is released from the balloon 3842 to expel the expansion fluid 3802 directly into the drainage lumen 3812. Thereby quickly deflating the balloon 3842. Since there is no intermediate structure between the balloon dilation fluid 3802 and the drainage lumen 3812, the rate at which the balloon 3842 is deflated is fast. One way to speed up the contraction may be to mold the contraction ports 3860, 3862 into a funnel-shaped configuration that opens outwardly from the outer wall 3840 toward the interior of the catheter 3800. Another way to speed up the contraction is to have two or more contraction ports 3860 around the circumference of the lumen inner wall 3810, or to enlarge the cross-sectional area of the contraction ports 3860, 3862, or both. Could be to do.

  The intermediate portion 4436 is not unbroken, but instead is either a small tubular arc (not shown) or even a plurality of arcs (not shown), or the two tubular portions 4432, 4434 together. It can be just a line (not shown) connecting to the. As such, the stretch valve tube 4430 defines an intermediate flexible gap 4438. In such a configuration, the stretch valve tube 4430 is more flexible when made of the same material as the other stretch valve tubes described herein because less material is used. When made of a less flexible material, the shortened proximal and distal portions 4432, 4434 combined with the thin intermediate portion 4436 prevent the stretch valve tube 4430 from interfering with the insertion of the catheter 4500. Can be flexible enough. The same applies to the insertion of the stretch valve tube 4430 into the drainage lumen.

  Again, in contrast to the uninterrupted tube, with respect to FIGS. 46 and 47, the stretch valve assembly 4730 of the catheter 4700 of the present invention comprises a proximal coil portion 4632, a distal plug 4634, and a distal coil portion. 4436. As before, FIG. 47 shows the balloon portion of the catheter 4700 of the present invention with the balloon 3842 partially expanded. An annular lumen inner wall 3810 defines a drainage lumen 3812 therein. In one or more circumferential longitudinal extents around the lumen inner wall 3810, the inflation lumen wall 3820 defines an inflation lumen 3822 and a balloon inflation port 3824 that is fluidly coupled to the inflation lumen 3822. . In the catheter 4700 of the present invention, there may be more than one inflation lumen 3822 and a corresponding inflation port 3824, although only one is shown here. Lumen plug 3836 fluidly closes inflation lumen 3822 distal to inflation port 3824 so that all expansion fluid 3802 is directed into balloon 3842. Lumen plug 3736 can plug distally at any point or extension from inflation port 3724. Outer wall 3840 fluidly covers all of inner walls 3810 and 3820 and forms the exterior of balloon 3842 but does not cover the distal end of drainage lumen 3812. The outer wall 3840 is formed by any method described herein and will not be described in further detail here.

  In this exemplary embodiment, the stretch valve assembly 4630 is disposed in the drainage lumen 3812 so as not to impede drainage of the drained fluid (eg, urine). The proximal coil portion 4632 acts as a device for securing the stretch valve assembly 4630 within the drainage lumen 3812 and the intermediate coil portion 4636 acts as a means for the distal plug 4634 to move away from the contraction ports 3860, 3862. Therefore, the diameter of the proximal coil portion 4632 is larger than that of the intermediate coil portion 4636. Intermediate coil portion 4636 may have a loose coil pitch to allow the catheter body to bend without kinking. The diameter of the proximal coil portion 4632 can be any dimension that is adapted to allow unhindered fluid to flow through the drainage lumen 3812, while one exemplary proximal coil portion 4632 is resting or stationary. The outer diameter of the state is only slightly larger than the diameter of the drainage lumen 3812 (eg, the wall thickness of the tube can be between 0.07 mm and 0.7 mm). In comparison, the quiescent or steady state outer diameter of one exemplary intermediate coil portion 4636 is only slightly smaller than the diameter of the drainage lumen 3812. Thus, proximal movement of the fixed proximal coil portion 4632 pulls the intermediate coil portion 4636 and slides the distal plug 4634 away from the contraction ports 3860, 3862 and away in the proximal direction. Let One exemplary configuration of the distal plug 4634 is a heat-shrinked polyolefin attached to the coil with cyanoacrylate.

  The proximal coil portion 4632 of the stretch valve assembly 4630 is proximal to the proximal end of the contraction ports 3860, 3862 in this exemplary embodiment. The distal plug 4634 of the stretch valve assembly 4630 is not distal to the distal end of the balloon 3842 so that the balloon 3842 can be deflated. The distal plug 4634 can be anywhere between the two ends of the balloon 3842, but is shown in an intermediate position in FIG. The distal plug 4634 of the stretch valve assembly 4630 covers the contraction ports 3860, 3862 in the longitudinal direction when the valve is in a steady or non-actuated state. The distance of the distal overlap of the contraction ports 3860, 3862 will depend on the amount of extension required to actuate the stretch valve of the catheter 4700 of the present invention, as will be described below.

  In order to secure the stretch valve assembly 4630 to the catheter 4700, a proximal anchor portion in addition to the stretch valve assembly 4630 is not required. Here, the proximal anchor portion is the proximal coil portion 4632 which, if it can be expanded to its original diameter, anchors itself within the drainage lumen 3812 so that unhindered fluid causes the drainage lumen 3812 to move. Fit to flow through. The length of the proximal coil portion 4632 in the longitudinal direction is as long as desired when installed in place, provided that the stretch valve assembly 4630 is securely secured within the drainage lumen 3812 in the longitudinal direction. The length may be too short or too long. The anchor portion 4632 is proximal to the proximal end of the balloon 3842 in this exemplary embodiment, but may be further inside (distal) of the balloon 3842, or closer to the balloon 3842 than shown. It may be a rank. In another exemplary embodiment, an adhesive or glue secures the proximal coil portion 4632 of the stretch valve assembly 4630 in a longitudinal direction in place within the drainage lumen 3812. The adhesive may be the same material as any or all of the walls 3810, 3820, 3840, or may be a different material. Illustrative, not shown, a fixation port or set of fixation ports formed through inner wall 3810 proximal to the proximal end of balloon 3842 and around proximal coil portion 4632 of stretch valve assembly 4630 In an embodiment, for example, if the outer wall 3840 is formed by immersing the inner part including the inner wall 3810 and the inflation lumen wall 3820 in a liquid bath of the same material as the double lumen extruded body, the outer wall 3840 is , Integral with both the inner wall 3810 and the inflation lumen wall 3820 and fixedly coupled to the proximal coil portion 4632 via the locking port (s).

In such a configuration, therefore, any proximal movement of the catheter 4700 at or proximal to the drainage ports 3860, 3862 will cause the stretch valve assembly 4630 to move proximally. That is, the distal plug 4634 of the stretch valve assembly 4630 can slide proximally within the drainage lumen 3812. When the catheter 4700 is still inflated when a force is applied, when the proximal end of the catheter 4700 is pulled to a force that is not greater than just before urethral bladder transition or urethral damage occurs, the force is, for example, 1 The distal plug 4634 is slid proximally with a tensile force in the range of 15 to 15 pounds (4.448 to 66.72 Newtons) to release the drainage ports 3860, 3862. In another exemplary embodiment, the range of force required to achieve the contraction point is between 1 and 5 pounds (4.448 to 22.24 Newtons) , particularly 1.5 to 2 pounds (6.672). To 8.896 Newton) .

  One exemplary method for installing the stretch valve assembly 4630 in the drainage lumen 3812 is to place the coil of the proximal coil portion 4632 on a mandrel having a diameter equal to or smaller than the inner diameter of the intermediate coil portion 4636. It is temporarily folded and held in place. The crimped proximal coil portion 4632 is then inserted into the drainage lumen 3812 to the point of implantation or fixation. The crimped proximal coil portion 4632 can then be expanded, thereby draining the proximal portion of the stretch valve assembly 4630 with the intermediate coil portion 4636 and the distal plug 4634 movably disposed. Secure to lumen 3812.

  Proximal and intermediate coil portions 4632, 4636 may be made from a single coil that is two different diameters, or two different pitches, or both.

  The catheters 200, 300, 1000, 1600, 2100, 2400, 2700, 3300, 3400, 3500, 3600, 3700, 3800, 4200, 4300, 4500, 4700 according to the present invention can be used for blood vessel related applications. All blood vessels have a tearable pressure. The balloon is used for a coronary artery, for example. If the coronary balloon is ruptured, the damage is less if the rupture is controlled by the present invention. The same applies to renal blood vessels or iliac blood vessels. In such situations, separable catheters improve them by making existing catheters safe. From a urological point of view, a separate balloon can not only prevent injury, but can signal the technician that he or she needs to get the help of a doctor or urologist regarding catheter insertion.

Claims (22)

A safety catheter,
A flexible multilumen shaft having an outer diameter, a distal tip, a shaft proximal portion, and a catheter proximal end comprising a drain end and an inflation end, wherein the flexible multilumen shaft is ,
A drain lumen extending through the shaft and shaped to allow fluid near the distal tip to pass through and drain from the drain end;
A distal hollow balloon portion defining a balloon interior and having at least one inflation port fluidly coupled to the balloon interior, wherein the balloon portion passes through the at least one inflation port and A distal hollow balloon portion that extends outwardly to a diameter greater than the outer diameter;
At least one inflation lumen parallel to the drain lumen and fluidly coupled to the interior of the balloon via the at least one inflation port, wherein the at least one inflation lumen is an expansion fluid and the balloon At least one inflation lumen shaped to expand the interior;
A drainage port fluidly connecting at least one of the balloon interior and the at least one inflation lumen to the drain lumen;
A flexible multi-lumen shaft that defines
A hollow stretch valve,
Arranged concentrically on the drain lumen and shaped to allow the fluid to pass therethrough,
Disposed in the drain lumen to prevent fluid from passing through the drainage port in a steady state;
Having a valve distal end,
In the extended state in which the proximal end of the catheter is extended, the sliding portion having a sliding portion that is slidably disposed at the distal end of the valve in the drain lumen. Sliding to allow the expansion fluid to pass through the drainage port;
A safety catheter comprising a hollow stretch valve. The safety catheter of claim 1, wherein the stretch valve has the extended state when a tensile force of 4.448 newtons to 66.72 newtons is applied to the axial proximal portion. The safety catheter of claim 1, wherein the stretch valve has the extended state when a tensile force of 4.448 newtons to 22.24 newtons is applied to the axial proximal portion. The safety catheter of claim 1, wherein the stretch valve has the extended state when a tensile force of 6.672 Newton to 8.896 Newton is applied to the axial proximal portion. When the balloon portion is inflated with fluid and a tensile force greater than 66.72 Newton is applied to the axial proximal portion, the stretch valve fills the stretched condition, thereby causing the expanded hollow balloon to The safety catheter of claim 1, which contracts. When the balloon portion is inflated with fluid and a tensile force greater than 22.24 Newton is applied to the axial proximal portion, the stretch valve fills the stretched state, thereby causing the expanded hollow balloon to The safety catheter of claim 1, which contracts. When the balloon portion is inflated with fluid and a tensile force greater than 8.896 Newton is applied to the axial proximal portion, the stretch valve fills the stretched condition, thereby causing the expanded hollow balloon to The safety catheter of claim 1, which contracts.   The safety catheter of claim 1, wherein the drainage port fluidly connects the interior of the balloon and the at least one inflation lumen with the drain lumen.   The safety catheter of claim 1, wherein the drainage port is a plurality of drainage ports that fluidly connect the drain lumen with the balloon interior and at least one of the at least one inflation lumen. The stretch valve has a valve proximal end that is a fixed portion that is fixedly coupled within the drain lumen;
The valve distal end of the stretch valve is the sliding portion slidably disposed within the at least one inflation lumen;
The safety catheter according to claim 1. A safety catheter,
A flexible multi-lumen shaft having an outer diameter, a distal tip, a shaft proximal portion, and a catheter proximal end comprising a drain end and an inflation end, the flexible multi-lumen shaft A drain lumen extending through the shaft and operable to drain fluid near the distal tip therethrough and out of the drain end;
A distal hollow balloon portion defining a balloon interior and having at least one inflation port fluidly coupled to the balloon interior, wherein the balloon portion passes through the at least one inflation port and A distal hollow balloon portion shaped to expand outwardly to a diameter greater than the outer diameter;
At least one inflation lumen parallel to the drain lumen and fluidly coupled to the interior of the balloon via the at least one inflation port, wherein the at least one inflation lumen is an expansion fluid and the balloon At least one inflation lumen shaped to expand the interior;
A drainage port fluidly connecting the interior of the balloon to the drain lumen;
A flexible multi-lumen shaft that defines
A hollow stretch valve,
Arranged coaxially to the drain lumen and shaped to allow fluid to pass therethrough,
Disposed in the drain lumen to prevent fluid from passing through the drainage port in a steady state;
Having a valve distal end,
In the extended state in which the proximal end of the catheter is extended, the sliding portion having a sliding portion that is slidably disposed at the distal end of the valve in the drain lumen. Sliding to allow the expansion fluid to pass through the drainage port;
A safety catheter comprising a hollow stretch valve. The safety catheter of claim 11, wherein the stretch valve has the extended state when a tensile force of 4.448 newtons to 66.72 newtons is applied to the axial proximal portion. The safety catheter of claim 11, wherein the stretch valve has the extended state when a tensile force of 4.448 Newtons to 22.24 Newtons is applied to the axial proximal portion. The safety catheter of claim 11, wherein the stretch valve has the extended state when a tensile force of 6.672 Newton to 8.896 Newton is applied to the axial proximal portion. When the balloon portion is inflated with fluid and a tensile force greater than 66.72 Newton is applied to the axial proximal portion, the stretch valve fills the stretched condition, thereby causing the expanded hollow balloon to The safety catheter of claim 11, which contracts. When the balloon portion is inflated with fluid and a tensile force greater than 22.24 Newton is applied to the axial proximal portion, the stretch valve fills the stretched state, thereby causing the expanded hollow balloon to The safety catheter of claim 11, which contracts. When the balloon portion is inflated with fluid and a tensile force greater than 8.896 Newton is applied to the axial proximal portion, the stretch valve fills the stretched condition, thereby causing the expanded hollow balloon to The safety catheter of claim 11, which contracts.   The safety catheter of claim 11, wherein the drainage port fluidly connects the interior of the balloon and the at least one inflation lumen to the drain lumen. The drainage port is a plurality of drainage ports, each fluidly connecting the interior of the balloon to the drain lumen;
The hollow stretch valve is
Disposed in the drain lumen to prevent fluid from passing through the plurality of drainage ports in a steady state;
The sliding portion slidably disposed within the drain lumen, wherein the sliding portion slides within the drain lumen in an extended state in which the proximal end of the catheter is extended; Having the sliding portion to allow expansion fluid to pass through the plurality of drainage ports;
The safety catheter according to claim 11. The stretch valve has a valve proximal end as the fixed portion fixedly coupled within the drain lumen;
The valve distal end of the stretch valve is the sliding portion slidably disposed within the drain lumen;
The safety catheter according to claim 11. A safety catheter,
A flexible multi-lumen shaft having an outer diameter, a distal tip, a shaft proximal portion, and a catheter proximal end comprising a drain proximal end and an inflation proximal end, the flexible multi-lumen The axis of the expression is
A drain lumen extending through the shaft and operable to drain fluid near the distal tip through the drain proximal end;
A distal hollow balloon portion defining a balloon interior and having at least one inflation port fluidly coupled to the balloon interior, wherein the balloon portion passes through the at least one inflation port and A distal hollow balloon portion operable to expand outwardly to a diameter greater than the outer diameter;
At least one inflation lumen parallel to the drain lumen and fluidly coupled to the at least one inflation port, the at least one inflation lumen expanding the interior of the balloon with an inflation fluid. At least one inflation lumen operable;
A drainage port fluidly connecting at least one of the balloon interior and the at least one inflation lumen to the drain lumen;
A flexible multi-lumen shaft that defines
A hollow stretch valve,
Disposed coaxially to the drain lumen and operable to allow fluid to pass therethrough;
Disposed in the drain lumen to prevent fluid from passing through the drainage port in a steady state;
Having a valve distal end and a valve proximal end;
A fixed portion at the proximal end of the valve that is fixedly coupled within the drain lumen;
In the extended state in which the proximal end of the catheter is extended, the sliding portion having a sliding portion that is slidably disposed at the distal end of the valve in the drain lumen. Sliding to allow the expansion fluid to pass through the drainage port;
With a hollow stretch valve,
A safety catheter having a multi-lumen shaft extending distally of the coupling portion of the fixed portion, which is relatively easier to extend than at least a portion of the multi-lumen shaft proximal to the spread . A safety catheter,
A flexible multi-lumen shaft having an outer diameter, a distal tip, a shaft proximal portion, and a catheter proximal end comprising a drain end and an inflation end, the flexible multi-lumen shaft A drain lumen extending through the shaft and operable to drain fluid near the distal tip therethrough and out of the drain end;
A distal hollow balloon portion defining a balloon interior and having at least one inflation port fluidly coupled to the balloon interior, wherein the balloon portion passes through the at least one inflation port and A distal hollow balloon portion operable to expand outwardly to a diameter greater than the outer diameter;
At least one inflation lumen parallel to the drain lumen and fluidly coupled to the at least one inflation port, the at least one inflation lumen expanding the interior of the balloon with an inflation fluid. At least one inflation lumen operable;
A drainage port fluidly connecting the interior of the balloon to the drain lumen;
A flexible multi-lumen shaft that defines
A hollow stretch valve,
Disposed coaxially to the drain lumen and operable to allow fluid to pass therethrough;
Disposed in the drain lumen to prevent fluid from passing through the drainage port in a steady state;
Having a valve distal end and a valve proximal end;
A fixed portion at the distal end of the valve that is fixedly coupled within the drain lumen;
In the extended state in which the proximal end of the catheter is extended with the sliding portion slidably disposed within the drain lumen at the proximal end of the valve, the sliding portion is within the drain lumen. Sliding to allow the expansion fluid to pass through the drainage port;
With a hollow stretch valve,
A safety catheter having a multi-lumen shaft extending distally of the coupling portion of the fixed portion, which is relatively easier to extend than at least a portion of the multi-lumen shaft proximal to the spread .