Patent Publication Number: US-2023149207-A1

Title: Apparatus and method for everting catheter for iud delivery and placement in the uterine cavity

Description:
CROSS-REFERENCE TO RELATED APPLICATIONS 
     This application is a continuation of U.S. patent application Ser. No. 17/185,449 filed Feb. 25, 2021, which is a divisional application of U.S. patent application Ser. No. 17/067,352, filed Oct. 9, 2020, which claims priority to U.S. Provisional Patent Application No. 62/913,160, filed Oct. 9, 2019, the contents of which are incorporated by reference herein in their entireties. 
    
    
     BACKGROUND 
     The apparatuses and methods disclosed herein can have utility for everting catheters that are characterized with an inner catheter, outer catheter, and everting membrane that can be connected to both catheters. The inner catheter may contain an inner lumen to pass fluid or media, drugs or therapeutic agents, instruments or devices such as intrauterine uterine devices (IUDs), endoscopes, and other catheters. 
     For physicians and medical professionals, accessing systems for vessels and bodily cavities in patients have typically used various guidewire and catheter technologies. In some cases, the process requires the insertion of a series of mandrels or wires to increase the lumen diameter for the eventual passage of a larger bore instrument within the vessel. This technique can be referred to as “Dottering” or in the case of accessing the cervical canal and uterus, physicians will use a series of increasing diameter mandrels known as Hegar dilators. In the techniques described above, the methods involved pushing an object, mandrel, or device through the vessel to gain access to a desired region in the body. The result of pushing an object, mandrel, or device creates shear forces on the lumen wall. In some cases, the shear forces can result in trauma, pain for the patient, or perforation. 
     In contrast, another access technology that has been used in prior art is referred to as an everting catheter. Everting catheters utilize a traversing action in which a balloon is inverted and with the influence of hydraulic pressure created by a compressible or incompressible fluid or media, rolls inside out or everts with a propulsion force through the vessel. Everting balloons have been referred to as rolling or outrolling balloons, evaginating membranes, toposcopic catheters, or linear everting catheters such as those in U.S. Pat. Nos. 5,364,345; 5,372,247; 5,458,573; 5,472,419; 5,630,797; 5,902,286; 5,993,427; 6,039,721; 3,421,509; and 3,911,927; all of which are incorporated herein by reference in their entireties. These are categorized as everting balloons and are for traversing vessels, cavities, tubes, or ducts in a frictionless manner. In other words, an everting balloon can traverse a tube without imparting any shear forces on the wall being traversed. Because of this action and lack of shear forces, resultant trauma can be reduced and the risk of perforation reduced. In addition, as a result of the mechanism of travel through a vessel, material and substances in the proximal portion of the tube or vessel are not pushed or advanced forward to a more distal portion of the tube or vessel. 
     In addition, as the everting catheter deploys inside out, uncontaminated or untouched balloon material is placed inside the vessel wall. In the inverted or undeployed state, the balloon and the IUD are housed inside the catheter body and cannot come into contact with the patient or physician. As the balloon is pressurized and everted, the balloon material rolls inside out without contacting any element at the entrance outside of the vessel. For the delivery of IUDs, the action of the balloon material rolling inside out also prevents the IUD to contact any element at the vaginal wall, exocervix, endocervical canal, and depending upon the depth of insertion, the internal cervical os of the patient. Another advantage of an everting balloon catheter is that the method of access is more comfortable for the patient since the hydraulic forces “pull” the balloon membrane through the vessel or duct as opposed to a standard catheter that needs to be “pushed” into and through the vessel or duct. For the delivery of IUDs, the hydraulic forces “pull” the balloon membrane and IUD through the cervix and into the uterine cavity as opposed to a standard IUD catheter tube that needs to be “pushed” into and through the cervix and into the uterine cavity. 
     For access to the uterine cavity with larger devices, the method typically used by physicians for accessing the cervical canal in women requires the use of multiple instruments of increasing diameter. The physician will use a small uterine sound or small diameter probe or Hegar device for gaining initial entry into the uterus via the cervix. Ever increasing sizes of Hegars are used to stretch the cervical muscles until the desired internal diameter is achieved for the insertion of a secondary instrument such as an endoscope or other device. This process can be particularly difficult in some nulliparous women who are seeking contraception with an IUD or women elect to use a hormonal IUD for alleviating abnormal bleeding. Post-menopausal women can also present with very small diameter cervical canals. A cervix could be difficult to traverse as a result of prior surgery, underlying stenosis, or other anatomical configuration or tortuosity that makes the passage of instruments or Hegar dilators difficult. 
     There are some cervical dilators that provide radial expansion to open the cervical canal to a greater internal diameter without the insertion of multiple instruments. All of these devices are predicated on first crossing or traversing the cervical canal prior to the step of radial expansion. Once traversed through the cervical canal, these devices use either mechanical means or the expansion of a balloon dilation member that is concentric on the exterior of the dilator probe. If the cervical canal is particularly tight or narrow, a small diameter probe or mandrel may be required to first cross the cervix and access the uterine cavity. As mandrels or instruments get smaller in diameter, the likelihood of perforation or a false passage increases. In any case, these cervical dilators require passage or crossing by the initial probe prior to any further radial expansion being performed. 
     Everting catheters have been described as dilatation catheters. Representative examples of dilating everting catheters include U.S. Pat. Nos. 5,364,345 and 4,863,440, both of which are incorporated by reference herein in their entireties. 
     Everting catheters have also been described with additional elements such as a handle for controlling instruments within an everting catheter. A representative example is U.S. Pat. No. 5,346,498 which is incorporated by reference herein in its entirety. Everting balloon catheters can be constructed with an inner catheter with an internal lumen or through-lumen (or thru-lumen). The through-lumen can be used for the passage of instruments, media, materials, therapeutic agents, endoscope, guidewires, or other instruments or devices. Representative samples of everting catheters with through-lumens are in U.S. Pat. Nos. 5,374,247 and 5,458,573. In addition, everting catheters have been described with waists or a narrowing of the balloon diameter, such as in U.S. Pat. No. 5,074,845, which is incorporated by reference herein in its entirety. 
     Everting catheters are particularly useful for accessing the uterine cavity where the endocervical canal may be stenotic, tortuous, or contain the presence of a C-section scar or other anatomical configuration that makes the passage of instruments difficult for the physician. This in turn can lead to an uncomfortable procedure for the patient. 
     One common gynecological procedure is the placement of IUDs for women who are either seeking a non-permanent method of birth control or medication from an intrauterine device that elutes hormonal treatment for abnormal uterine bleeding, painful periods, or other medications that may be placed by an implant in the uterine cavity. IUDs can contain copper and can be configured in numerous configurations. In all of these cases, the physician needs to place the device within the uterine cavity. 
     For the placement of IUDs in the uterus, IUD inserters consist of fairly stiff tubes or cannula for insertion. The IUD implant itself can be configured in a “T-shape” or “Y-shape” in its natural, uncollapsed state in which the three arms of the “T” or “Y” are constructed as rigid members that can flex, but are not easily bent in a tight radius less than 0.500″. The “T” or “Y” configuration is needed to maintain the IUD within the uterine cavity during the normal activities of the woman and otherwise more forceful activities such as exercise, coughing, and the uterine contractions that occur with menses. In these situations, the “T” or “Y” shape is needed to prevent expulsion or migration from the uterine cavity since the arms of the “T” or “Y” are designed to keep the IUD near the patient&#39;s fundus with its rounded ends approximating the bilateral cornua of the uterine cavity. Not all IUDs are “T” or “Y” shaped and other configurations including circular or coiled shaped are known or available commercially. 
     In clinical use during device placement, the endocervix may have multiple turns and curvatures that contain tight radii curves. For placement through the endocervix and to straighten the cervical canal to reduce the amount of curvature, the physician needs to grasp the cervix and maintain counter-traction on the cervix. Besides straightening the cervix, the counter-traction facilitates pushing the IUD inserter through the endocervical canal and into the uterine cavity. Misplacements, perforations, or the inability to place the IUD, are all known and recognized outcomes or adverse events with an IUD placement procedure. The stiffness of the cannula and the IUD implant itself also leads to patient discomfort during the placement procedure. This is particularly true for women who have stenotic cervices or who are nulliparous. 
     Once the IUD is in the proper position in the patient, the IUD inserter can have a cannula that is attached to a handle that allows the physician to translate the IUD from out of the distal end of the cannula. The handle allows the physician to perform the placement procedure with one hand. 
     Following the placement of the IUD in the uterine cavity, the IUD inserter is withdrawn from the patient. The retrieval suture or sutures of the IUD remains in the patient&#39;s endocervical canal when sliding the inserter out of the cervix. Once removed, the physician can trim the visible sutures extending from the exocervix. The IUD sutures are visible in the patient&#39;s vagina emanating from the exocervix and can be trimmed to length as indicated by the IUD manufacturer&#39;s labeling. 
     Also, when delivering an IUD, instruments, devise, and reproductive material such as an embryo, into the uterine cavity, the access system can push cervical mucus or fluids and materials from the vagina into the uterine cavity. There is a potential that these fluids and materials from the vagina could promote bacterial infection. The action of the unrolling balloon is designed to minimize this effect. 
     In addition, access systems for the uterine cavity can create a vacuum effect when the access system is being withdrawn or removed from the uterine cavity. This vacuum effect can unintentionally remove the reproductive material from the uterine cavity in the situation of embryo transfer. In existing systems, when the transfer catheter is retracted from a second outer or guiding catheter (e.g., the “inner” catheter), the retraction produces vacuum pressure within the uterine cavity. This vacuum pressure is created in the uterine cavity by the removal and backward movement of the transfer catheter within the inner catheter. After the embryo transfer is completed, an embryologist may inspect the transfer catheter to verify that the embryos or reproductive material was indeed deposited in the uterus and not pulled back into the transfer catheter because of the vacuum effect. The same procedure may be done for the outer catheter once this catheter is removed. For IUD placement, having a system that can potentially reduce vacuum effect can lead to more reliable and exact IUD placement. 
     Further, everting balloons describe an action in which a balloon is inverted and, with the influence of hydraulic pressure created by a compressible or incompressible fluid or media, rolls inside out or everts with that propulsion force. Everting balloons have been referred to as rolling or outrolling balloons, evaginating membranes, toposcopic catheters, or linear everting balloons. These are all categorized as everting balloons due to their property of traversing vessels, cavities, tubes, or ducts in a substantially frictionless manner. Everting balloons can traverse a tube without imparting any significant shear forces on the wall being traversed. Because of this action and lack of shear forces, material and substances in the proximal portion of the tube or vessel are pushed or advanced forward to a more distal portion of the tube or vessel. For example for 1 everting balloons in the female reproductive tract, potentially infectious substances from the vagina, cervical os or exocervix, or the legs or other anatomy of the patient, and the hands of the physician during insertion or catheter preparation, are not in contact with the everted balloon that resides in the catheter system prior to deployment in the patient. The objective of keeping the everting balloon isolated from potentially uncleanly surfaces is to reduce post-procedural infections. 
     SUMMARY OF THE INVENTION 
     An everting balloon system is disclosed. The everting balloon system can be used for IUD placement, delivery of instruments, devices, and endoscopes, and insemination, urinary incontinence, dilation of a body lumen, for access and sealing within a body cavity, or combinations thereof. The system can have automatic deployment and disengagement. The system can have a handle for insertion. The system can have a motorized air or fluid pump or pressurization source. The system can have inner and outer catheters that can automatically disengage upon everting. 
     The everting balloon system can have an intubating base with a locking balloon that can activate upon pressurization. The system can be a compact, low profile unit used in vivo. The system can be single use and disposable. The system can be non-irritation and non-infection causing. 
     The everting balloon system can be used for cervical access, dilation, and the delivery of IUDs. The everting balloon system can have a system handle mechanism that can enable a one-handed operating technique by the user. The one-handed operating technique can include advancement and pressurization of the everting balloon membrane within the control of the user with one hand. 
     The everting balloon system can be used for the insertion of drug delivery devices, or insemination, and can seal the cervix for a duration of time for the deposition of drug agent or sperm and to allow for mobility for the patient. The everting balloon system can have a decoupling mechanism configured to decouple the outer catheter and inner catheter while maintaining hydraulic pressure in an everting balloon. The system can deflate and removal the everting balloon concurrently. 
     The system can be used to place or deliver fallopian tube inserts (i.e., intratubal inserts, such as the Essure device from Bayer Corporation) in fallopian tubes. The system can access the intramural and isthmic portions of the fallopian tube. All or part of the everting catheter system can be loaded into a hysteroscope and placed with direct endoscopic visualization. 
     The everting catheter system can be a selective fallopian tube catheter with a curved distal end section and angled ball tip. This configuration can be performed by ultrasound or radiographic visualization. 
     One or more fallopian tube occluding devices (e.g., the Essure device) can be loaded into the everting balloon system, for example, in the through lumen of the inner catheter. Once fully everted and placed into the fallopian tube, the everting balloon system, such as the inner catheter, can be withdrawn from the fallopian tube while leaving the fallopian tube occluding device in the fallopian tube. Once the everting balloon system is withdrawn from the fallopian tube, the fallopian tube occluding can be deployed (e.g., device anchors such as coils can be extended, or a resilient porous matrix can expand to friction fit the tube lumen). Once the fallopian tube occluding device is deployed, a central guidewire can be removed from the fallopian tube. The procedure can be repeated for the contralateral fallopian tube. 
     The everting balloon system can be used to access the bladder, ureters, kidneys, or combinations thereof. Devices, tools, instrumentation, endoscopes, drugs, therapeutic agents, sampling devices (brushes, biopsy, and aspiration mechanisms), or combinations thereof can be delivered through the inner catheter lumen to the target site. 
     Specialized everting catheter systems with specific instruments, tools, or functions built or placed within the everting catheter system are also disclosed herein. Examples of such tools or instruments are biopsy devices, cytology devices, drug delivery mechanisms, fluid delivery mechanisms, endoscopes, IUDs, or other tools to be delivered into a bodily cavity, a bodily space, a potential bodily space that is created by the everting balloon mechanism, or a bodily vessel. There are several advantages to having an IUD built or placed into the everting catheter system as the delivery mechanism. The everting balloon can be used to pull the IUD implant into the uterine cavity without requiring the physician or operator to push an inserter through the endocervix and into the uterine cavity. This is particularly useful for tortuous or tight cervices. In addition, the everting membrane rolls inside-out through passageways in a frictionless manner without imparting shear forces on the inner lumen wall. The everting balloon works to protect the body passageway from the distal end profile of the IUD while pulling the IUD into the desired location. 
     The IUD can be fixed to the everting catheter system and automatically extends beyond the distal end of the everting balloon by being pulled by the everting balloon into the uterine cavity. During the eversion process, the IUD can be shielded from the body tissue until it extends beyond the distal end of the everting balloon. In this process the IUD will not contact the vagina, exocervix, or other fluids, mucus, or tissue in the proximal region of the endocervix. Providing the IUD at a specific distance in the everting catheter system can provide the physician the ability to direct the IUD to an exact distance from the exocervix or specific location in the uterine cavity. 
     An IUD placement procedure can be performed or delivered in particular locations in the uterine cavity. 
     An everting membrane for IUD placement can be designed for one-handed placement. 
     An everting membrane for IUD placement can be designed for one-handed placement with automatic negative pressure during the release of the IUD. 
     An everting membrane for IUD placement can be designed for one-handed placement with automatic or manual irrigation through the central lumen during the release of the IUD. The automatic irrigation can facilitate device placement by releasing the IUD from the everting membrane. Irrigation through the central lumen prior to loading the IUD within an everting catheter, or the delivery and release of the IUD in the everting membrane, by increasing the lubricity or the IUD within the everting membrane so that the IUD can slide out of the everting membrane with reduced friction. Equipping the everting catheter for IUD delivery and placement with an irrigation function is especially useful since some IUDs contain hormonal drugs, coatings, or other therapeutic agents that can be tacky when interacting against the surface of certain polymers that are useful in catheter fabrication. 
     The irrigation mechanism, whether done automatically or manually, can be used to facilitate device visualization in the uterine cavity using ultrasonography, fluoroscopy, or direct visualization with an endoscope through the central lumen of the IUD inserter. The injection of saline as an example with the irrigation mechanism through the central lumen can provide the physician a slightly distended uterine cavity in which ultrasonographic visualization of the IUD in the uterine cavity for confirmation of IUD placement. 
     The IUD system can have a transfer mechanism to facilitate the loading of commercially available or second party IUDs in the everting catheter. Once loaded with the IUD, the everting catheter is ready for placement into the patient&#39;s uterus. The transfer mechanism includes a loading apparatus of retrograde loading the second-party IUD into the distal end of everting membrane and a snare for capturing and retracting the IUD sutures through the central lumen of the everting catheter. The entire mechanism is contained within a flat stand that will fit on a standard procedure prep table. In operation, the loading mechanism can facilitate loading of a second party IUD within an everting catheter prior to delivery into a patient. 
     An everting catheter system for an IUD placement procedure can be a facilitated by an aspiration system for holding onto the device during the initial steps of device loading. The aspiration system can work in conjunction with the distal end opening of a pusher through the central lumen of the everting catheter to stabilize and pull the IUD into position with the everting membrane of the everting catheter system. 
     An everting catheter system for an IUD placement procedure can utilize a translatable outer catheter with telescoping sections that provides selected insertion depths within the uterine cavity for IUD device placement. Telescoping sections in the outer catheter can independently change and select the insertion depth of the IUD placement without altering any other component of the everting catheter system. 
     The distal end of the everting membrane at the location of the IUD can have an echogenic marker for increased ultrasound contrast, visibility, and detection within the patient&#39;s uterus or enhanced real time visualization of IUD placement. 
     An IUD loading system can allow the user to load a separately supplied IUD into an everting catheter system. The loading system can include a cradle, split tube, and tray fixture to facilitate IUD loading into the everting catheter system. 
     Another embodiment uses a derivation of the loading system within the manufacturing process during the construction of an integrated everting system with a pre-loaded IUD. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         FIGS.  1 A through  1 E  are longitudinal cross-sectional views of the distal end of a variation of a method for using the everting balloon system. 
         FIG.  2 A  illustrates a variation of the everting balloon system in a fully everted configuration. 
         FIG.  2 B  is a cross-sectional view of a variation of the system handle. 
         FIG.  3 A  illustrates a variation of the distal end of the everting balloon system with the dilating balloon in a less than fully inflated configuration. 
         FIG.  3 B  illustrates a variation of the distal end of the everting balloon system with the dilating balloon in a fully inflated configuration. 
         FIG.  4 A  illustrates a variation of the everting balloon system with a syringe in an attached, but not yet deployable configuration. 
         FIG.  4 B  illustrates a variation of the everting balloon system with the syringe in an attached and deployable configuration. 
         FIG.  4 C  illustrates a variation of the everting balloon system of  FIG.  4 B  with the plunger driver shown in cut-away. 
         FIG.  5 A  illustrates a length of a variation of the everting balloon system. 
         FIG.  5 B  is a partial cross-sectional view of a variation of the system of  FIG.  5 A . 
         FIGS.  5 C and  5 D  are variations of side and perspective views of a portion of cross-section A-A. 
         FIG.  5 E  is an exploded view of a variation of a portion of the system handle and the drive gears. 
         FIG.  5 F  is a close-up view of a variation of the system handle at the ratchet handle axle. 
         FIG.  6 A  is a cross-sectional view of a variation of the system handle. 
         FIGS.  6 B through  6 D  are side, top perspective and cross-sectional views, respectively, of a variation of the everting balloon system with the system handle of  FIG.  6 A . 
         FIGS.  7 A and  7 B  are exploded and perspective views, respectively, of a variation of the everting balloon system. 
         FIG.  8 A  is a cross-section view of a variation of the three-way connector and adjacent elements in a configuration to deliver media pressure to the outer catheter, for example to the everting balloon. 
         FIG.  8 B  is a cross-section view of a variation of the three-way connector and adjacent elements in a configuration to deliver media pressure to the inner catheter, for example to the dilating balloon. 
         FIG.  9    is an exploded view of a variation of a transfer catheter. 
         FIGS.  10 A through  10 C  illustrate a variation of method for delivering material to a target site, such as reproductive material delivered to a uterine cavity. 
         FIGS.  11 A through  11 C  illustrate a variation of a method for delivering material to a target site, such as reproductive material delivered to a uterine cavity. 
         FIGS.  12 A to  12 E  illustrate an everting catheter for performing an IUD placement procedure with an everting membrane. 
         FIGS.  13 A to  13 I  illustrate in both side views and top views additional derivations built into the distal end of the everting membrane and inner catheter. 
         FIGS.  14 A through  14 D  illustrate further embodiments demonstrating the advancement and release of an IUD within an everting membrane. 
         FIGS.  15 A through  15 D  illustrate an automatic one-handed eversion mechanism for IUD placement. 
         FIGS.  16 A to  16 J  illustrate a variation of an everting catheter that can deliver an IUD within the uterine cavity. 
         FIGS.  17 A to  17 I  illustrate a variation of an everting catheter that can deliver an IUD within the uterine cavity. 
         FIGS.  18 A to  18 C  illustrate mechanisms for automatically providing negative pressure during the IUD release step of the delivery process. In addition, irrigation through the central lumen can be provided separately or in conjunction with negative pressure to facilitate the IUD release step. 
         FIG.  19 A  illustrates an everting catheter system for delivering an IUD. 
         FIGS.  19 B to  19 D  are close-up views of the everting catheter system. 
         FIG.  20 A  illustrates the everting catheter system after full eversion of the balloon in the process of delivering an IUD. 
         FIG.  20 B  is a close up view of the distal end of the everted balloon and IUD. 
         FIG.  20 C  is a close up view of the proximal portion of the everting catheter system after full eversion in the process of delivering an IUD. 
         FIGS.  21 A to  21 C  illustrate the process of delivering an IUD within a simulated uterine cavity model. 
         FIGS.  22 A to  22 E  illustrate a packaging configuration for the transit and loading of the everting catheter system for delivering an IUD. 
     
    
    
     DETAILED DESCRIPTION 
     An everting balloon system  2  (also referred to as an everting catheter system) that can be used to traverse a vessel, such as the cervical canal is disclosed. The everting balloon system  2  can be used to access the uterine cavity via the cervix. The cervical canal is a single lumen vessel that can stretch or dilate. The everting balloon system  2  can have a control system that can be operated with one hand. The everting catheter system can also traverse other locations in the body of a patient or animal for the purposes of placement of a device within a bodily cavity or lumen. 
       FIGS.  1 A through  1 E  illustrate that an everting catheter system  2  can have a radially outer catheter  4 , a balloon membrane  6 , and a radially inner catheter  8 . The inner catheter  8  can have an inner catheter lumen  10  (e.g., a through-lumen). The distal end of the inner catheter lumen  10  can be open or closed. The inner catheter  8  can have the inner catheter lumen  10  or be a solid rod or flexible mandrel. The everting balloon system  2  can have a media volume  12 . The media volume  12  can be the contiguous open volume between the inner catheter  8  and outer catheter  4  that is proximal to the balloon membrane  6 . A radially outer terminal perimeter of the balloon membrane  6  can be attached to the distal terminal end of the outer catheter  4 . A radially inner terminal perimeter of the balloon membrane  6  can be attached to the distal terminal end of the inner catheter  8 . The everting balloon system  2  can be made without an inner catheter  8 , for example with the balloon membrane  6  extending proximally out of the working area to a control device (e.g., a pump). 
       FIG.  1 A  illustrates that the everting catheter system  2  can be in an unpressurized configuration. The media volume  12  can be uninflated and unpressurized. The balloon membrane  6  can be slack. 
       FIG.  1 B  illustrates that that everting catheter system  2  can be in a pressurized and uneverted configuration. A pressurization device, such as a pump, for example at the proximal end of the everting catheter system  2  can be in fluid communication with the media volume  12 . The pressurization device can deliver a fluid media, such as a pneumatic gas or hydraulic liquid media (e.g., saline, water, air, carbon dioxide, or combinations thereof), at a media pressure  14  to the media volume  12 . The media pressure  14  in the everting balloon  2  can be from about 2 to about 5 atmospheres of pressure when in the everted configuration and higher media pressures  14  from about 5 atmospheres to 10 atmospheres are possible, for example, to provide greater everting capability for more difficult or stenotic passageways in the body. 
     The balloon membrane  6  can inflate and be in tension. The balloon membrane  6  can block the distal port of the inner catheter lumen  10 . 
       FIG.  1 C  illustrates that the everting catheter system can be in an inflated and partially everted configuration. The inner catheter  8  can be translated distally, as shown by arrow  16 , with respect to the outer catheter  4 , and out of the outer catheter  4 . The distal terminal end of the inner catheter  8  can be proximal of the distal terminal end of the balloon membrane  6 . The distal terminal end of the inner catheter  8  can be proximal or terminal of the distal terminal end of the outer catheter  4 . The balloon membrane  6  can block the distal port of the inner catheter lumen  10  or can be open allowing fluid communication between the inner catheter lumen  10  and the target site. 
       FIG.  1 D  illustrates that the everting catheter system can be in an inflated, fully everted, and fully distally extended configuration. The inner catheter  8  can be translated distally, as shown by arrow  16 , with respect to the outer catheter  4  until the distal terminal end of the inner catheter  8  is longitudinally beyond or co-terminal with the distal terminal end of the balloon membrane  6 . The distal port of the inner catheter lumen  10  can be unobstructedly accessible and in fluid communication with the target site. 
     In the fully inflated configuration, the balloon membrane  6  can form an inflated everting balloon  18 . The everting balloon  18  can have a balloon outer diameter  20  and balloon length  22  in the inflated and fully everted configuration. 
     The balloon outer diameter  20  can be from about 2 mm to about 20 mm, more narrowly from about 2 mm to about 7 mm, for example about 5 mm. The outer diameter can be constant or vary along the length of the everting balloon  18 . For example, for use in the cervical canal, the most proximal portion of the everting balloon outer diameter  20  could be configured with a smaller outer diameter than the remainder of the everting balloon membrane  24 . As an example, the first proximal portion of the everting balloon  18  can have a smaller balloon outer diameter  20  such as from about 2 mm to 4 mm for a length of from about 5 mm to about 10 mm from the distal terminal end of the outer catheter  4 , and the remainder of the length (e.g., from about 4 cm to about 7 cm along the everting balloon  18 ) of the everting balloon  18  can have a balloon outer diameter  20  from about 4 mm to about 7 mm. The outer diameter of the proximal end of the everting balloon  18  can have a consistent balloon outer diameter  20 , for example for delivery in the cervix or urethra, of from about 3 mm to about 6 mm, and the distal-most outer about 2 cm to about 3 cm of the everting balloon  18  can have a balloon outer diameter  20  from about 10 mm to about 20 mm, for example to create a seal with and anchor in the internal cervical os of the uterine cavity or the bladder. 
     The exterior surface of the balloon membrane  6  can be configured with ridges, projections, bumps, grooves, and additional surface or mechanical features, or combinations thereof, for example for increased friction or holding power within the vessel, or the entrapment of bodily fluids, cells, or tissue. 
     The everting balloon length  22  can be from about 2 cm to about 31 cm, more narrowly from about 2 cm to about 25 cm (e.g., for use in a male urethra), yet more narrowly from about 2 cm to about 12 cm for placement of IUDs, yet more narrowly from about 3 cm to about 6 cm for invitro fertilization, insemination procedures, or the delivery of instruments and endoscopes, for example about 4 cm, about 7 cm, about 15 cm and about 30 cm. 
       FIG.  1 E  illustrates that the everting catheter system can be in an inflated and partially or fully everted configuration. A device or tool  26 , liquid, gas, or combinations thereof can be translated, as shown by the arrow  28 , through the inner catheter lumen  10 , out of the distal port of the inner catheter lumen  10  and into the target site. The tool  26  can be an IUD, a biopsy tool, a scope, a sonogram probe, a plug, a cauterization tool, or combinations thereof. Suction can be applied from the proximal end of the inner catheter lumen  10 , and to the target site, for example removing debris from the target site through the inner catheter lumen  10 . 
     To retract and reposition or remove the balloon membrane  6 , the inner catheter  8  can be pulled proximally to pull the balloon membrane  6  back within the outer catheter  4 . The balloon membrane  6  can be deflated or have media pressure  14  reduced and the entire system can be withdrawn from the target site. 
       FIG.  2    illustrates that the everting balloon system  2  can have a system handle  30 . The system handle  30  can have a system handle connector  32 . The system handle  30  can be attached to the outer catheter  4  and the inner catheter  8 , for example at the system handle connector  32 . The system handle connector  32  can be removably attached to the outer catheter  4 . For example, the outer and inner catheters  4 ,  8  and balloons can be detached from the system handle  30  and replaced. The system handle  30  can be sterilizable. Media (e.g., liquid or gas) delivered by the system handle  30  can be filled into the system handle  30  before attaching or replacing the catheters and balloons. 
     The system handle  30  can have a rigid system handle case  34  and a rigid pump lever  36  rotatably attached to the system handle  30  case at a pump lever axle  38 . 
     The system handle  30  can have an inlet port  40 . The everting balloon system  2  can have a pressurization source. The pressurization source can have a flexible liquid reservoir  42  or fluid supply container or bag. The fluid bag can be filled with a hydraulic and/or pneumatic fluid. 
     The inlet port  40  can be a female luer fitting and connection. The inlet port  40  can be in fluid communication through an inlet-reservoir channel  44  with the flexible reservoir  42 . The liquid reservoir  42  can be between the rigid pump lever  36  and a rigid system handle case  34 . The inlet port  40  can extend out of the proximal end of the system handle case  34 . The inlet port  40  can be configured to attach to a liquid source (e.g., a hose, tube, or supplemental reservoir configured to deliver the liquid through the inlet port  40  and to the liquid reservoir  42 ). The inlet port  40  can have a proximal check valve or one-way valve configured to allow flow to the liquid reservoir  42  and prevent backflow (e.g., proximal flow from the liquid reservoir  42  and out the inlet port  40 ). 
     The liquid reservoir  40  can be in one-way (e.g., via a check valve) or two-way fluid communication with the media volume  12 . 
     When the liquid reservoir  42  contains liquid, the pump lever  36  can rotate away from the system handle case  34 , as shown by pump lever rotation arrows  46 , as the liquid reservoir  42  inflates. The pump lever  36  can be rotated toward the system handle case  34  to compress the liquid reservoir  42 , for example, forcing liquid from the liquid reservoir  42  and into the media volume  12  of the everting balloon  18 . 
     The pump lever  36  can provide a pumping (e.g., suction) action to supply aspiration to withdraw liquid from the media volume  12  of the everting balloon  18 . A spring within the lever can facilitate the pumping action of the lever to open the lever (not shown) for each compression. 
     The system handle  30  can have an advancement slide  48 . The advancement slide  48  can be proximally and distally translatable, as shown by arrow  50 , with respect to the system handle case  34 . The advancement slide  48  can be configured to translate the inner catheter  16  with respect to the outer catheter  4 . For example, pushing the advancement slide  48  distally can push the inner catheter  8  distally with respect to the outer catheter  4  and evert the everting balloon  18 . Pulling the advancement slide  48  proximally can pull the inner catheter  8  proximally with respect to the outer catheter  4  and retract the everting balloon  18 . The advancement slide  48  can have gear wheels, ratchets with racks, and rotating advancement screws. 
     The advancement button can be an advancing ratchet or a roller wheel that is geared into or with the inner catheter  8  to allow for translation of the inner catheter  16 . 
     With one hand, the physician can advance the inner catheter  8 , evert the everting balloon  18 , traverse the cervical canal with the everting balloon  18 , and access the uterine catheter through the inner catheter lumen  10 . 
     The fluid reservoir  42  can be pressurized prior to placement of the distal tip of the outer catheter  4  at the cervix. The fluid reservoir  42  can has a proximal check or one-way valve on the proximal portion of the handle. The proximal check valve is the connection point for the physician to pressurize the system. The distal portion of the fluid bag can be attached to a distal pressure check valve  52  that can open when pressure from the fluid bag is at or above a distal check valve limit pressure, for example about 1 atmosphere of pressure from the liquid reservoir, and then deliver liquid and pressure from the liquid reservoir  42  to fill and pressurize the media volume  12  of the catheters and everting balloon  18 . The distal pressure check valve  52  can be a one-way valve allowing hydraulic or pneumatic fluid or media to go from the fluid reservoir  42  to the media volume  12  of the catheters and everting balloon  18 . Higher and lower atmosphere pressure ratings from 1 atmosphere are also possible for the distal pressure check valve  52  such as from about 0.5 atmospheres to about 2 atmospheres. 
     During pressurization of the fluid reservoir  42  (e.g., by pumping with the pump lever  36  or from the inlet port via the proximal check valve  54 ), pressures greater than a reservoir limit pressure (e.g., 1 atmosphere) of the distal pressure check valve  52  can open the distal pressure check valve  52  and allow fluid media to flow from the liquid reservoir  42  into the media volume  12  of the catheters and everting balloon  18 . The pressurization in the media volume  12  of the catheters and everting balloon  18  can unroll and evert the everting balloon  18  under hydraulic force. Excess media can remain in the fluid reservoir  42  after the everting balloon  18  fully everts. 
     The distal pressure valve  52  can be connected to a three-way connector  56  (e.g., Y-connector or T-connecter) that has a hemostasis valve  58 , for example a Touhy-Borst valve. Thus the fluid reservoir  42  can stage or hold additional potential hydraulic pressure to be stored in the system for the user (e.g., physician) to use as needed by rotating the pump lever  46  without a change of hand position or the use of a second hand. 
     The inner catheter  8  can extend through the three-way connector  56 . The inner catheter  8  can translate (i.e., advance and retract) through the three-way connector  56  while maintaining a seal (i.e., without the media volume  12  of the catheters or everting balloon  18  losing pressure). The inner catheter  8  (e.g., if a solid rod or mandrel) can be configured to withstand hydraulic pressures of up to about 5 atmospheres or up to about 10 atmospheres during the everting process and translational (e.g., advancement, retraction, tensile, compression, or combinations thereof) forces of up to about 2 pounds or up to about 5 pounds without deformation. As an example, during the everting process the inner catheter  8  with an inner catheter lumen  10  (e.g., a through lumen) could withstand media pressures  14 , tensile and compressive forces, and rotational forces as the everting balloon membrane  6  traverses curved or tortuous anatomy, to allow for the passage of an instrument, catheter, media, or materials within the through lumen. Movement of the advancement button on the handle moves the inner catheter  8  within the three-way connector  56  and through the outer catheter  4 . The everting balloon  18  can then evert and roll out of the outer catheter  4  and traverse the target site (e.g., the cervical canal). 
     After accessing the target site, for example, the user can activate the pressure release control  60  to release or reduce the pressure from the media volume  12  thereby deflating or reducing the outer diameter of the everting balloon  18 , and/or manually withdraw the everting balloon  18  and inner catheter  8  by retracting the advancement slide  48  or pulling the system handle  30  proximally, and therefore the remainder of the system. 
     Once the biological lumen to be traversed (e.g., the cervical canal, or urethra) is traversed by the everted balloon  18 , the everting balloon system  2  can increase the pressure in the everting balloon  18 , for example increasing the diameter of the everting balloon  18 , or while maintaining a constant diameter everting balloon  18  (e.g., for a fiber-reinforced everting balloon  18  or a balloon membrane  6  constructed from a less distensible material). The pump lever  36  can be compressed to increase pressure in the fluid reservoir  42  builds and exits the distal pressure check valve  52 . The proximal check valve  54  can prevent or minimize the fluid media (e.g., pneumatic or hydraulic pressure) from leaking or bleeding in the proximal direction and out of the inlet port  40 . 
     The user can rotate the pump lever  36 , for example increasing the pressure in the fluid reservoir  42 , the media volume  12 , and the everting balloon  18 . The balloon outer diameter can then increase, further pushing open the diameter of the biological lumen. For example, the everting balloon  18  can dilate the cervix and cervical canal. Tools such as endoscopes, instruments, Hegars, other devices to increase the diameter of the cervix further, or combinations thereof, can then be inserted into the dilated cervical canal concurrent with the everting balloon system  2  being located in the cervical canal or subsequent to the everting balloon system  2  being withdrawn from the cervical canal. 
     The pump lever  36  can deliver tactile feedback to the user indicating the pressure of the everting balloon  18 . The everting balloon system  2  can have a pressure gauge indicating the pressure in the media volume  12 , such as in the liquid reservoir  42  and/or the media volume  12  in the catheters and everting balloon  18 . 
     The system handle  30  can have a pressure release control  60 , such as a toggle lever or knob. The pressure release control  60  can release fluid from the liquid reservoir  42  and/or media volume  12  of the catheters and everting balloon  18 . 
     The pressure release control  60  can be connected to the hemostasis valve  58 . The hemostasis valve  58  can have a seal or sealing gasket. The pressure release control  60  can be configured to open and close the sealing gasket by rotating the sealing cap, or open a connection to a separate drainage tube (not shown) in fluid communication with the media volume  12 . 
     The pressure release control  60  can be on the handle  30  positioned by the user&#39;s thumb position, distal to and collinear with the movement of the advancement slide  48 . The pressure release control  60  can be operated by the same hand as the user is operating the advancement slide  48  and pump lever  36 . 
     The pressure release control and handle can be used to advance and deliver an IUD with one hand by the user. 
     The user can perform the following operations of the everting balloon system  2  with a single hand (e.g., without their other hand or another operator) without a change of hand position:
         a. pressurize the liquid reservoir  42 ,   b. position or place the distal end of the everting balloon system  2  at the patient&#39;s cervix;   c. control the everting balloon system  2  position throughout use;   d. advance the inner catheter  8  and balloon membrane  6 ;   e. increase the diameter of the everting balloon  18  by pumping additional hydraulic pressure from the fluid reservoir  42 ;   f. retract the inner catheter  8  and balloon membrane  6 ; and   g. activate the pressure release control  60  to remove or release pressure from the everting catheter system.       

     Structurally, the buttons and actuators to enable these functions can be positioned on the handle to allow for the operator to manipulate these features without a change of hand position or requiring the use of the other hand. For instance, advancement and retraction of the inner catheter  8  can be performed by a slide mechanism or gear wheels that are located on the upper side of the handle approximately 4 inches from the proximal end of the handle or handle grip. Levers and ratchet mechanisms can be located on the lower or underneath side of the handle at a distance of from about 2 inches to about 4 inches from the proximal end of the handle grip. Additional actuators can be placed on the lateral sides of the handle grip from about 3 inches to about 4 inches from the proximal end of the handle grip or on the upper or lower portions of the handle grip from about 3 inches to about 4 inches from the proximal end. The button and actuator position can be palpable for the operator without requiring visual confirmation, thereby-allowing the user to maintain eye contact with the patient or visualization source such as an endoscopic monitor or ultrasound image. 
     During the use of the everting balloon system  2 , the user can utilize their other hand for handling an ultrasonic probe, a tenaculum (e.g., if the cervix is difficult to access by anatomical reasons or is severely retroverted or anteverted), stabilizing the patient or other instruments, or combinations thereof. 
       FIG.  3    A illustrates that the inner catheter  8  can be attached to a dilating balloon  62  or inner catheter balloon. The dilating balloon  62  can be radially inside of the everting balloon  18 . The distal end and the proximal end of the dilating balloon  62  can be attached and sealed to the inner catheter  8 . The inner catheter  8  can have a dilating balloon port  64  longitudinally within the dilating balloon  62 . The dilating balloon port  64  can be in fluid communication with a fluid pressure source at the proximal end of the everting balloon system  2 , for example in or attached to the system handle  30 . The dilating balloon  62  can be inflated and deflated through the dilating balloon port  64 . 
     The dilating balloon  62  can be more, the same, or less compliant than the everting balloon  18 . The everting balloon  18  wall can be thicker, thinner, or the same thickness as the dilating balloon  62  wall. The everting balloon  18  can be made from one or more polymers including silicone, urethane, rubber, latex, polyethylene, polyolefin, irradiated polyolefin combined with ethylene vinyl acetate, co-polymers such as polyether block amide (PEBA, also known as Pebax), a fiber-reinforced polymer, PET, nylon, or combinations thereof. The dilating catheter can be made from any of the materials mentioned for the everting balloon  18 . 
     The everting and/or dilating balloon membrane  6  can have a thickness from about 0.001 in to about 0.004 in. 
     The everting and/or dilating balloon  18 ,  62  can be internally coated with a lubricious material such as silicone oil, mineral oil, other lubricant, or combinations thereof. The lubricous coating can reduce the friction within the balloon during eversion. 
     The exterior of the everting and/or dilating balloon  18 ,  62  can be smooth, for example the balloon can be made by tubing extrusion. The balloons can be blow molded. For example, the exterior surface of the balloon can have ridges or other surface protrusions, for example to increase friction or holding forces in the target body lumen (e.g., cervical channel or urethra). The outer diameter of the balloons can vary dimensionally For instance, the most distal portion of the everting balloon  18  can be manufactured with a larger outer diameter to accommodate larger vessel sizes or inflation that can extend into the bladder. 
     During use, the everting balloon  18  can pull the inner catheter  8  into the endocervical canal. When the everting balloon  18  is deployed into the cervical channel, the dilating balloon  62  can be positioned in the cervical channel. 
       FIG.  3 B  illustrates that the dilating balloon  62  can be inflated by delivering pressurized fluid through the dilating balloon inflation port  64 . The dilating balloon  62  can expand inside of the everting balloon  18 . The dilating balloon  62  can inflate to a dilating balloon diameter  66 . 
     The dilating balloon  62  can have a predetermined or molded size and shape. For example, the dilating balloon  62  can have a dilating balloon diameter  66 . For example, the maximum dilating balloon diameter  66  or maximum everting balloon diameter can be from about 2 mm to about 12 30 mm, and for some applications, up to about 20 mm in diameter (e.g., for use in a cervix), and more narrowly from about 2 mm to about 10 mm (e.g., for use in a urethra), more narrowly from about 6 mm to about 12 mm, yet more narrowly from about 2 mm to about 7 mm (e.g., for use in a urethra), yet more narrowly from about 3 mm to about 4 mm (e.g., for use in a male urethra). The dilating balloon  62  can inflate to a preset outer diameter. (The dilating balloon outer diameter  66  can be equal to or less than the dilating diameter needed for the body lumen, such as the cervix.) The everting balloon  18  can have a maximum everting balloon diameter equal to or less than the maximum dilating balloon diameter  66 . 
     The dilating balloon  62  can be inflated to the same or a higher pressure than the everting balloon  18 . For example, the dilating balloon  62  can have a dilating balloon pressure from about 4 atmospheres to about 12 atmospheres of pressure, and up to about 20 atmospheres of pressure, for example for disrupting a pathological stenosis or condition within a bodily lumen. 
     When the dilating balloon  62  is inflated, the everting balloon  18  can stretch due to the expanding dilating balloon  62  to the dilating balloon diameter  66 . The inflation media within the everting balloon  18  can remain inside the balloon or be withdrawn before, during, and/or after inflation of the dilating balloon  62 . Due to the frictional forces of the everting balloon membrane  6  on the bodily lumen in the everted state, for example, the everting balloon membrane  6  can serve to maintain the position of the dilating balloon  62  during the dilation process without unintentional advancement or retraction of the system within the bodily lumen during the dilatation process. 
     The dilating balloon  62  can inflate and tear or break the everting balloon  18  as the everting balloon diameter expands beyond the strain limit for the everting balloon  18 . The inflation media within the everting balloon  18  can remain inside the balloon or be withdrawn before, during, and/or after inflation of the dilating balloon  62 , for example exiting the everting balloon  18  can exit when the everting balloon  18  tears open. 
     The everting balloon  18  can break or tear along an intentional line upon the inflation of the dilating catheter. For example, the everting balloon  18  can be tom by a mechanical instrument on or within the outer catheter  4 , a sharp implement on the proximal portion of the inner catheter  8  that becomes active upon full eversion and inflation of the dilating balloon  62 , and/or further advancement of the inner catheter  8  that disengages the attachment or bond between the everting balloon  18  and the inner catheter  8  on the distal end of the inner catheter  8 . The tearing or splitting of the everting balloon  18  can be done be weakening the everting balloon  18  with a mechanical indentation or seam on the balloon membrane  6  that splits upon reaching a specific strain limit, such as along a helical line, lateral line, longitudinal line, or combinations thereof. The everting balloon membrane  24  can be manufactured with increased longitudinal axial orientation of the molecular structure by tensioning or expanding the membrane along the longitudinal axis of the balloon during the balloon forming process which can promote a longitudinal break if the everting balloon membrane  24  splits or tears. A radial tear in the everting balloon  18  can be promoted by manufacturing the balloon membrane  6  with greater radial orientation of the molecular structure by radially expanding or tensioning the balloon membrane  6  during the balloon forming process. 
     The system handle  30  can hold the inflation media to be delivered to and from the everting balloon  18  and the dilating balloon  62 . The inflation media can be in the liquid reservoir  42  (e.g., the fluid bag or a syringe piston). The inflation media can be delivered, for example via valves, to the dilation balloon after the inflation and eversion of the everting balloon  18 . The system handle  30  can have gear wheels or a ratchet configured to advance the inner catheter  8 . The outer catheter  4  can extend about 25 cm distal to the system handle  30 . The system handle  30  and actuators can inflate the everting balloon  18  and dilating balloon  62  from control with one hand. 
     The dilating balloon  62  can be positioned into and dilate the cervix. 
       FIGS.  4 A through  4 C  illustrate that the inner catheter  8  can be in a fully retracted position inside of the outer catheter  4 . 
       FIG.  4 A  illustrates that the system handle  30  can have a pump lever  36 , such as a ratchet handle  68 , a syringe connector  70 , and a plunger drive plate  72 . The ratchet handle  68  can have a finger grip, trigger, lever, pump mechanism, or combinations thereof. The fluid reservoir can be a syringe  74 . The syringe  74  can have a volume from about 5 cc to about 20 cc, for example about 5 cc or about 20 cc. An open distal port of the syringe can be attached to and in fluid communication with the syringe connector  70 . The syringe connector  70  can have the distal pressure valve  52 . The syringe connector  70  can be rotatably attached to the system handle case  34 . The syringe  74  can have a plunger  76  longitudinally translatable with the remainder of the syringe  74 . The syringe  74  can be filled with any media disclosed herein, such as saline, air, gas, or combinations thereof. The liquid reservoir  42  can have two separate syringes  74 , each attached to and in fluid communication with the same or different syringe connectors  70 . For example, a first syringe can be in fluid communication with the everting balloon  18 , and the second syringe can be in fluid communication with the dilation balloon  62 . 
     The syringe  74  can be locked to the syringe connector  70 . 
     The outer catheter  4  can have an outer catheter distal tip  78 . The outer catheter distal tip  78  can be, for example, an atraumatic tip such as an acorn tip or stop. The outer catheter distal tip  78  can be configured to prevent insertion of the outer catheter  4  too far into the target biological lumen (e.g., the endocervix). 
     The outer catheter distal tip  78  can have an outer catheter distal port  80 . The outer catheter distal port  80  can be large enough to allow the inner catheter  8  and balloons to pass through. 
       FIG.  4 B  illustrates that the syringe connector  70  and syringe  74  can rotate, as shown by the arrow, so the longitudinal axis of the syringe  74  can be parallel or collinear with the longitudinal axis of the outer catheter  4 . The syringe connector  70  can be angularly fixed with respect to the rest of the system handle  30 . The plunger drive plate  72  can be rotated and/or translated to contact or almost contact the proximal end of the syringe plunger  76 . 
       FIG.  4 C  illustrates that the system handle  30  can have a plunger driver  82 . The plunger driver  82  can have a linear rack or plunger drive screw  84 , plunger drive collar  86 , and plunger drive plate  72 . The ratchet handle  68  can be squeezed to rotate the plunger drive screw  84 , as shown by arrow  87 , or linear rack. The plunger drive screw  84  or linear rack can be configured to translate the plunger drive collar  86 . For example, the plunger drive collar  86  can have internal threads engaging with outer threads of the plunger drive screw  84 . The plunger drive collar  86  can be translatably fixed to the plunger drive plate  72 . The plunger drive collar  86  and plunger drive plate  72  can translate distally with respect to the remainder of the syringe  74  when the ratchet handle  68  is squeezed. The plunger drive plate  72  can be in contact with and press the plunger  76  in a distal direction as shown by arrow. 
     The ratchet handle  68  can have a ratchet to prevent reversing the direction of the plunger driver, for example to prevent proximal translation of the plunger  76 . A release lever can be rotated or deployed to release the ratchet mechanism for disengagement of the assembly, withdrawal of the system, or redeployment. The ratchet handle  68  can have no ratchet or a two-way ratchet, for example controlling the direction of the plunger driver  82 , for example to allow proximal and distal translation of the plunger  76 . The plunger drive plate  72  can be fixed to or touching but unfixed to the plunger  76 . 
     Squeezing the ratchet handle  68  can depress the syringe plunger  94 . Depressing the syringe plunger  94  can force inflation media from the syringe  74  to the media volume  12  of the dilation and/or everting catheter  18 , for example pressurizing the respective balloons. 
       FIGS.  5 A through  5 F  illustrates that the system handle  30  can have a stop cock and check valve  88  extending from the three-way connector  56 . The stop cock and check valve  88  can be in fluid communication with the media volume  12 . The stop cock and check valve  88  can be outside (as shown) or inside of the system handle case  34 . The stop cock and check valve  88  can be accessed to add media, remove media, or check the pressure of the media in the media volume  12 . 
     The system handle  30  can have one or more syringe detents  90 . The syringe detents  90  can removably attach to a portion of the syringe  74  to prevent or minimize longitudinal translation of the syringe  74  with respect to the system handle case  34 . The syringe detent  90  can be configured to allow the syringe  74  to slide in and out of the detent transverse to the longitudinal axis of the syringe  74 . 
     The system handle case  34  can have a deflecting plate  92 . The outer and/or inner catheters  4 ,  8  can press against the deflecting plate  92 . The deflecting plate  92  can alter or deflect the path of the outer and inner catheters  4 ,  8  towards the longitudinally axial direction of the target site. The deflecting plate  92  can have a molded or formed groove, pins, plate, panel, or combinations thereof. The outer catheter  4  can be manufactured with a preset curve to accommodate the curved path within the system handle case  34 . 
     The system handle case  34  can have a handle grip  96 . The inner catheter  8  can have a linear inner catheter grip length  98 . The inner catheter grip length  98  can be a length of the inner catheter  8  in the uneverted state in the handle grip  96 . The inner catheter grip length  98  can be about 12 cm of inner catheter  8  in the uneverted state, for example corresponding to an eversion length for the inner catheter grip length  98  of about 6 cm (e.g., about 50% of the inner catheter grip length  98 ) of everted balloon membrane  24 . Alternatively, the inner catheter  8  can be configured to coil up on wheel, have telescoping segments, or have folding and unfolding segments, to reduce the amount of distance needed within a system handle case  34  to accommodate the length of inner catheter  8  in the uneverted state. 
     The system handle  30  can have a reservoir-catheter channel  100 , for example in fluid communication with the distal end of the syringe  74  and the proximal end of the inner catheter  8 . The reservoir-catheter channel  100  can be a tube from the syringe connector  70  to the inner catheter  8 . 
     The system handle  30  can have an access channel  102  extending from an external surface of the system handle connector  32  to an external surface of the system handle case  34 . The access channel  102  can proximally terminate at a proximal access port  104 . 
     The inner catheter  8  can extend through the access channel  102 . One or more tools or fluids can be inserted through, and/or suction can be applied to, the proximal access port  104  and access channel  102  into and through or adjacent to the inner catheter  8 . 
     The system handle  30  can have one or more drive gears  106 . The drive gears  106  can be on one or opposite sides of the access channel  102 . The drive gears  106  can encroach or impinge into the access channel  102 . The drive gears  106  can be rotatably attached to the system handle case  34  via drive gear axles  108 . The drive gears  106  can have teethed gear sections and drive gear grooves  124 . The inner catheter  8  can extend through the drive gear grooves  124 . The drive gears  106  can frictionally push and pull the inner catheter  8 . One or more of the drive gears  106  can extend and be exposed out of the system handle case  34 . For example, the exposed drive gears  106  can be rotated by pressing on the exposed drive gear  106  with the user&#39;s palm or digit (e.g., thumb). The exposed drive gear  106  can be interdigitally engaged with one or more non-exposed drive gears  106 . Rotating a first one of the drive gears  106  can rotate other drive gears  106  interdigitally engaged with the first drive gear  106 . 
     The system handle case  34  can have a system handle case first lateral portion  110  and a system handle case second lateral portion  112 . The system handle  30  can be made by attaching the system handle case first lateral portion  110  to the system handle case second lateral portion  112 . Each drive gear axle  108  can be rotatably attached to the system handle case first lateral portion  110  and the system handle case second lateral portion  112 . 
     The pump lever axle can be a ratchet handle axle  114 . The ratchet handle  68  can rotate around the ratchet handle axle  114 . 
     The system handle  30  can have a plunger drive rack  116 . The plunger drive rack  116  can be fixed to the plunger drive plate  72 . The plunger drive plate  72  can extend perpendicularly from the proximal end of the plunger drive rack  116 . A side of the plunger drive rack  116  facing toward the plunger drive plate  72  can have unidirectional or bidirectional drive teeth  118 . 
     The system handle  30  can have a ratchet handle spring  120  compressed between the system handle case  34 , and/or the ratchet handle  68 , and/or a ratchet arm  122 . The ratchet handle spring  122  can reset the ratchet handle  68 , for example by rotating the ratchet handle  68  forward, after the ratchet handle  68  has been squeezed. 
     The system handle  30  can have the ratchet arm  122  or actuating pawl. The ratchet arm  122  can be mechanically attached to the ratchet handle  68 , for example to the handle spring  120 . The ratchet arm  122  can be in a track limiting motion of the ratchet arm  122  to translation in the longitudinal direction with respect to the syringe  74 . The proximal terminal end of the ratchet arm  122  can be curved in a u-shape. The terminal end of the ratchet arm  122  can press against a ratchet tooth. The ratchet arm  122  can be configured to pull the plunger drive rack  116  distally when the ratchet handle  68  is squeezed. The ratchet arm  122  is configured to move proximally with respect to the plunger drive rack  116  when the ratchet handle  68  is returned to a reset position. 
     The system handle  30  can have a locking pawl (not shown) can be spring-loaded between the system handle case  34  and the plunger drive rack  116 , for example, allowing distal translation of the plunger drive rack  116  and preventing proximal translation of the plunger drive rack  116  except when the locking pawl is manually released from the plunger drive rack  116  by the release lever  126 . 
     The outer catheter  4  can have an outer catheter length  128 , as shown in  FIG.  5 B . The outer catheter length  128  can be from about 4 cm to about 35 cm, more narrowly from about 10 cm to about 24 cm, for example about 17 cm. 
       FIGS.  6 A through  6 D  illustrate that the system handle  30  can have an inner catheter drive tray  130  translatably attached to the system handle case  34 . A proximal length of the inner catheter  8  can extend proximally from the system handle case  34 . The proximal length of the inner catheter  8  can be in, on, or adjacent to the inner catheter drive tray  130 . 
     The syringe  74  can have a syringe loading connector  132 , such as a luer connector, at the terminal distal or proximal end of the syringe  74  (e.g., the end further from the system handle case  34 ). A delivery tube  133  or delivery device can be attached to the syringe loading connector  132  and pressurized media can be delivered through the syringe loading connector  132  into the syringe  74 . 
     The delivery tube  133  or delivery device can be disconnected from the syringe loading connector  132  before deploying the everting balloon  18 , as shown in  FIG.  6 C . The delivery tube  133  can wrap inside the handle grip  96  and connect the syringe  74  and its pressurization media to the three-way connector  56  and the hemostasis valve  58  or inlet port  40  for the dilation balloon  62 . 
     The proximal terminal end of the inner catheter  8  can be attached to the proximal access port  104 . The proximal end of the inner catheter drive tray  130  can have one or more access port detents  134 . The access port detents  134  can attach to the proximal access port  104 . The access port detents  134  can removably attach to a portion of the proximal access port  104  to prevent or minimize longitudinal translation of the proximal access port  104  with respect to the inner catheter drive tray  130 . The access port detent  134  can be configured to allow the proximal access port  104  to slide in and out of the access port detents  134  transverse to the longitudinal axis of the inner catheter drive tray  130 . 
     The inner catheter drive tray  130  can be translated along the longitudinal axis of the inner catheter drive tray  130  to translate the inner catheter  8  (e.g., advance the inner catheter  8  into the target site). The inner catheter can deliver an IUD, instrument, device, endoscope, or a dilating balloon. 
     The system handle case  34  can have a fluid connection between the syringe  74  and the outer catheter  4 , as disclosed herein. 
     The ratchet arm  122  can extend away from the drive rack  116  to form a release lever  126 , as shown in  FIG.  6 A . One or more other release levers  126  can extend from other locations on the system handle  30 , as shown in  FIGS.  6 B and  6 D . The release lever  126  can be rotated to disengage the ratchet arm  122  from the drive rack  116 . 
     The ratchet handle  68  can have a safety lock hole  136 . A safety lock having a cable or rod can removably extend through the safety lock hole  136 , for example to create an interference fit against the system handle case  34  and prevent rotation of the ratchet handle  68 , for example preventing unintentional or premature media delivery from the syringe  74 . 
     The ratchet handle  68  can be laterally split into a catheter sub-handle  138  and a media sub-handle  140 . The catheter sub-handle  138  can be configured to control the advancement of the inner catheter drive tray  130 . The media sub-handle  140  can be configured to control the pressure of media delivery from the syringe  74 . The catheter sub-handle  138  can be attached to an inner catheter drive rack. The media sub-handle can be attached to a plunger drive rack. 
     The ratchet handle  68  can control the syringe  74  for applying media pressure to the everting balloon  18  and dilating balloon  62 , and independently control the translational movement of the inner catheter  8 . 
       FIGS.  7 A and  7 B  illustrate that the inlet port  40  can have a female luer connector. The system handle connector  32  can have a female luer connector. The outer catheter distal tip  78  can have a soft rubber or polymerized acorn tip, for example, to assist in stabilizing the everting system  2  at the opening of the bodily lumen or preventing unintentional advancement of the outer catheter  4  within the bodily lumen. 
     The reservoir-catheter channel  100  can extend from the three-way connector  56  and out of the system handle case  34 . The proximal terminal end of the reservoir-catheter channel  100  can be attached to a female luer connector and/or the distal pressure valve  52 . The distal pressure valve  52  and/or female luer connector can be connected to the liquid reservoir  42  (not shown). 
       FIG.  8 A  illustrates that the three-way connector  56  can have a hemostasis valve  58 . The three-way connector  56  can have or be a Touhy-Borst Y-connector. The inner catheter  8  can extend through the three-way connector  56 . 
     The three-way connector  56  can have a distal gasket  142  between the reservoir-catheter channel  100  and the system handle connector  32 . The distal gasket  142  can have a cylindrical distal gasket port  144  extending through the radial middle of the distal gasket  142 . The distal gasket port  144  can have a distal gasket port diameter. 
     The three-way connector  56  can have a proximal gasket  146  proximal to the distal gasket  142 . The proximal gasket  146  can be between the reservoir-catheter channel  100  and the proximal outlet through which the inner catheter  8  proximally exits the three-way connector  56 . The proximal gasket  146  can be more, the same, or less compliant than the distal gasket  142 . The proximal gasket  146  can have a cylindrical proximal gasket port  148  extending through the radial middle of the proximal gasket  146 . The proximal gasket  146  can have a proximal gasket port diameter. 
     The inner catheter  8  can have an inner catheter small diameter length  150  and an inner catheter large diameter length  152  proximal to the inner catheter small diameter length  150 . The inner catheter  8  can have an inner catheter proximal inflation hole  154  at the distal end of the inner catheter large diameter length  152 . The inner catheter proximal inflation hole  154  can be in fluid communication with the open distal end of the inner catheter lumen  10  and/or the dilating balloon port  64 . 
     Positive media pressure  14  or flow can be delivered, as shown by arrows, through the reservoir catheter channel  100  to the three-way connector  56 . The inner catheter large diameter length  152  can occlude, plug, and/or seal the proximal gasket port  148 . The positive media pressure  14  or flow can be delivered through the gap between the outer diameter of the inner catheter  8  (e.g., along the inner catheter small diameter length  150 ) and the inner diameter of the distal gasket port  144  and to the media volume  12  between the outer catheter  4  and the inner catheter  8 , for example to the everting balloon  18 . 
       FIG.  8 B  illustrates that the inner catheter  8  can be translated distally, as shown by arrow, at least until the inner catheter large diameter length  152  moves into the distal gasket port  144 . The inner catheter large diameter length  152  can slide through the proximal gasket port  148 . The inner catheter large diameter length  152  can occlude, plug, and/or seal the distal gasket port  144  and/or against the distal gasket  142 . The media  155  flow from the reservoir-catheter channel  100  can be forced to flow into the inner catheter proximal inflation hole  154 . The media  155  can flow down the inner catheter lumen  10 , for example to the dilating balloon  62 . 
     An exemplary procedure for delivering an IUD (not shown) or dilating a body lumen such as the cervical canal can include:
         1. The syringe  74  can be loaded onto the system handle  30 . The system handle  30  can be a separate, reusable item in which the everting catheter and syringe filled with media  155  can be attached to the remainder of the system before use. Alternatively, the system handle  30  can come supplied to the end user preassembled with the remainder of the system and pre-filled, or combinations thereof.   2. The distal end of the everting balloon system  2  can be placed at the exocervix.   3. The ratchet handle  68  can be depressed. The first one to two clicks of the ratchet (i.e., as the locking pawl passes over ratchet teeth) can depress the syringe plunger  94  and pressurize the everting balloon  18 . The everting balloon  18  can be pressurized to 4 to 6 atmospheres.   4. The ratchet handle  68  can be depressed further (or released to rotationally reset and then depressed further). The next sets of clicks on the ratchet handle  68  can indicate advancement the inner catheter  8 . This can be accomplished by the ratchet mechanism rotating gear wheels on the inner catheter  8  and/or translating a linear rack to advance the inner catheter  8 .   5. The ratchet handle can be depressed further (or released to rotationally reset and then depressed further). The advancement of the inner catheter  8  can continue until the everting balloon is fully deployed and everted. The dilation balloon  62  can be positioned on the distal end of the inner catheter  8 .   6. The ratchet handle  68  can be depressed further. The next click of the ratchet can de-pressurize the everting balloon  18  or deliver an IUD (not shown).   7. The ratchet handle  68  can be depressed further. The next click of the ratchet can change the pressurization outlet of the syringe  74  from the everting balloon  18  to the dilation balloon  62  or this action can deliver an IUD (not shown). This can be accomplished, for example, by:
           a. rotating a valve with the ratchet mechanism,   b. manually rotating the valve, and/or   c. advancing the inner catheter  8  to where the inner catheter proximal inflation hole  154  or port is exposed to the inflation media, such as shown in  FIGS.  8 A and  8 B .   
           8. The ratchet handle  68  can be depressed further. The next sets of clicks on the ratchet can indicate the inflation of the dilatation balloon  62 .   9. The dilatation balloon  62  may rupture the overlying everting balloon  18 .   10. The amount of force in the biological lumen dilatation can be governed by a pressure relief valve or by the amount of volume of media  155  that can be placed within the dilatation balloon  62 . The dilatation pressure can be monitored by a pressure gauge in or attached to the system handle case  34 . The dilation balloon  62  can dilate the cervix with from about 6 atmospheres to about 20 atmospheres. The dilation balloon  62  can initially deliver about 10 atmospheres to about 12 atmospheres with a reduction in pressure as the cervix dilates and the dilatation process is completed. The system can deliver a known volume of media  155  into the dilation balloon  62  irrespective of quantifying or measuring the media pressure  14 .   11. The dilatation process may be observed by ultrasound or radiographic imaging.   12. A pressure relief button on the system handle  30  can be activated to remove or reduce dilatation pressure in the media volume  12  in the inner catheter lumen  10 .   13. The syringe plunger  94  may be retracted to draw vacuum from the inner catheter lumen  10  and dilation balloon  62 , for example loosening the dilation balloon  62  from the cervix, and/or deflating the dilation balloon  62 , for example to facilitate removal of the everting balloon system  2  from the cervix.   14. The everting balloon system  2  can be re-pressurized, for example if additional dilatation force is desired in the cervix. For instance, if an additional stenosis in the cervix is visible, the dilatation balloon  62  can be repositioned and inflated in the additional stenosis area.       

     The everting catheter system can access a bodily cavity (e.g., the uterine cavity or fallopian tubes) to deliver or introduce of tools (e.g., IUDs and instruments), reproductive (e.g., embryos, in vitro fertilization (IVF) or insemination products, such as hormones) media  155  or material, contrast media, dye, therapeutic agents, sclerosing agents to treat the endometrium, insufflation media, or combinations thereof to the cavity. For example, reproductive media can be delivered with a transfer catheter inserted through the inner catheter lumen  10  to the uterine cavity. 
       FIG.  9    illustrates that a transfer catheter  156  or insemination catheter can have a transfer connector  158 , such as a female luer connector, a strain relief length  160 , and a transfer tube  162 . The transfer tube  162  can hold the reproductive media. The transfer tube  162  can have a proximal length having a proximal length diameter larger than a distal length diameter of a distal length of the transfer tube  162 . A delivery force, for example a positive fluid pressure, can be delivered through the transfer connector  158  and strain relief length  160  to push the contents of the transfer tube  162  into the target site. 
     The transfer catheter  156  can attach to or inserted through the inlet port  40 . The transfer tube  162  can hold an embryo, for example for in vitro fertilization or IVF. The embryo transfer catheter  156  can deliver embryos through the system and to the uterine cavity. The transfer catheter  156  can hold spermatozoa and through the system and to the uterine cavity for intrauterine insemination procedures. The transfer catheter  156  can hold and deliver other materials the deposition of drugs, therapeutic agents, instruments, endoscopes, cytology brushes, other catheters, or combinations thereof through the system and into the uterine cavity. The transfer catheter  156  can be connected to a vacuum source for the aspiration of materials from the uterine cavity or other bodily cavities and lumens. 
     The transfer catheter  156  and/or materials can be loaded in the inner catheter lumen  10  prior to everting the everting balloon  18  within the vessel or bodily cavity. For example in the case of delivery of reproductive material in the uterine cavity, the transfer catheter  156  can be loaded with washed and prepared semen in the transfer tube  162  and the transfer catheter  156  can be placed in the inner catheter lumen  10 . 
     A guidewire can be inserted through the transfer catheter  156  and/or the remainder of the system, for example to direct the tube or system to the target site  164 . The guidewire can be used for recanalization. 
     The inner catheter  8  can be extended and the everting balloon  18  can evert and unroll through the cervix and into the uterine cavity. Concurrently or subsequently, the transfer catheter  156  can be advanced through the inner catheter lumen  10  into the uterine cavity. Once fully everted or when the transfer catheter  156  becomes extended or exposed from the inner catheter  8  and beyond the everting balloon membrane  24 , the reproductive material  166  in the transfer catheter  156  can be deposited by a syringe  74 , squeeze bulb, piston, or other pressure system. A second delivery catheter, such as a second insemination, IVF, or drug delivery catheter can be concurrently inserted into the inlet port  40  or a second inlet port. The second delivery catheter can be deployed to the target site  164  concurrent with or subsequent to the transfer catheter  156 . 
     The system handle  30  can have a lead-in area. The lead-in area can, for example, be without steps, edges, bumps, or restrictions that may impede or contact the distal opening of the transfer catheter  156  during passage, for example so that in the case of delivery of insemination material, the transfer catheter  156  can be easily loaded into the system handle  30 . An insemination syringe  74  or pump can be attached to the proximal transfer connector to deliver pressure to the transfer tube  162 , for example to expel the reproductive material  166  once the distal port of the transfer catheter  156  is positioned at the target site  164  (e.g., after the everting balloon  18  is fully deployed). The actuation of the insemination syringe or pump on a pre-loaded transfer catheter  156  can be performed by the same hand that holds and operates the components of the everting catheter system. 
     In addition, the transfer catheter  156  can be configured to be introduced into the proximal connector in the handle of the everting catheter system once the system is fully deployed. 
     The user can perform any or all of the following while using the everting balloon system  2 , for example with a single hand:
         a. pressurize the everting catheter system;   b. position the everting balloon system  2  at the patient&#39;s cervix;   c. maintain the everting balloon system  2  position throughout the procedure;   d. advance the inner catheter  8  and everting balloon  18 ;   e. once extended beyond the everting balloon membrane  24  or inner catheter  8 , present the transfer catheter  156  for deposition into the bodily cavity such as a uterine cavity   f. retract the inner catheter  8  and everting balloon  18 ; and/or   g. activate (e.g., toggle) the pressure release lever to remove or release hydraulic or pneumatic pressure from the media volume  12 .       

       FIGS.  10 A through  10 C  illustrate that the distal end of the everting balloon can form a balloon check valve  168 . The length of the everting balloon  18  distal to the distal terminal end of the inner catheter  8  can radially contract to form a tight orifice that can be the balloon check valve  168 . The balloon check valve  168  can be an openable barrier that can block or interrupt fluid communication between the inner catheter lumen  10  and the target site  164 . 
     The balloon membrane  6  can have from about 1 mm to about 3 mm of overlapping wall at the balloon check valve  168  closing off the inner catheter lumen  10 . The strength or closing pressure of the balloon check valve  168  can be modulated during use. For example the distance of overlap of balloon membrane  6  can be increased or decreased by controlling the amount of excursion available for the inner catheter  8  and everting balloon membrane  24 . 
       FIG.  10 B  illustrates that the distal end of the transfer catheter  156  can be advanced, as shown by arrow  170 , through the inner catheter lumen  10 , through the balloon check valve  168 , and to the target site  164 . The transfer catheter  156  can penetrate or push open the balloon check valve  168  when the transfer catheter  156  moves through the balloon check valve  168 . When the terminal distal end of the transfer catheter  156  is distal of the balloon check valve  168  and at the target site  164 , the reproductive material  166  loaded in the transfer catheter  156  can be delivered  172  through a distal port of the transfer catheter  156  and into the target site  164 , such as the uterine cavity. 
       FIG.  10 C  illustrates that the transfer catheter  156  can be retracted through the balloon check valve  168  and the inner catheter lumen  10  after the reproductive material is deposited at the target site  164 . The balloon check valve  168  can close as the transfer catheter  156  is retracted through the balloon check valve  168 . The balloon check valve  168  can maintain a seal between the inner catheter lumen  10  and the target site  164  when the transfer catheter advances  170  through, remains stationary within, and is retracted through the balloon check valve  168 . 
     The reproductive material  166  can be isolated from vacuum effect or the retraction of reproductive material  166  from the target site  164  as a result of the vacuum forces created by the withdrawal of the transfer catheter  156  through the system once the deposition of reproductive material  166  is completed. The balloon check valve  168  can reduce or eliminate vacuum effect for embryo transfer. 
     The balloon check valve  166  can be a tactile indicator for the physician when passing the transfer catheter  156  through the everting balloon system  2 . In transfer procedures, depending upon physician preference or patient anatomy, for example, the amount of insertion of the transfer catheter  156  through the distal end of the everting system can vary from patient to patient. As the distal end of the transfer catheter  156  passes through the balloon check valve  168 , the resistance created by the balloon check valve  168  can be felt by the physician on the proximal end of the transfer catheter  156 . Depending upon the length of balloon chosen to act as a balloon check valve  168 , the degree or amount of resistance can be modulated. In some procedural settings there may be a compromised ability to see the amount of insertion of the transfer catheter  156  into the everting balloon  18 , or physical depth indicia or markings on the proximal end of the transfer catheter  156 . The compromised ability to see may be due to low light within the procedure room so that imaging and visualization of monitors can be enhanced. In addition, the physical relationship of the physician, embryologist, or other persons or equipment in the procedure room may compromise the ability to see easily the amount of insertion into the everting catheter. The tactile sensation of the resistance of the balloon check valve  168  can create a palpable indicator that the transfer catheter  156  is at the distal end of the everting balloon  18 . 
     The everting balloon system  2  can be used to access and seal the uterine cavity, for example, for the deposition of reproductive material  172  for long duration intrauterine insemination. 
       FIGS.  11 A through  11 C  illustrate that the everting balloon membrane  24  can create a seal within the cervical canal (e.g., against the cervical canal walls  174 ) as the everting balloon  18  traverses the cervical canal.  FIG.  11 A  illustrates that the everting balloon membrane  24  can unroll and advance along the cervical walls, as shown by arrows, as the balloon is pressurized and the inner catheter  8  is distally advanced. The outer catheter  4  can also seal against the cervical canal wall  174  For example, the outer catheter  4  outer diameter can be equal to the everting balloon outer diameter. 
       FIG.  11 B  illustrates that the transfer catheter  156  can advance distally within the everting balloon  18  and the inner catheter lumen  10 . The transfer catheter  156  can deposit the reproductive material  166  (e.g., sperm) within the uterine cavity  176 . 
       FIG.  11 C  illustrates that the transfer catheter  156  and/or the inner catheter  8  can be retracted (e.g., from about 3 mm to about 10 mm) or inverted, as shown by arrows, to close the distal end of the inner catheter lumen  10 , as shown by arrows, with respect to the uterine cavity  176 . The distal opening of the balloon  178  can close, for example due to the pressure within the everting balloon  18  forcing the everting balloon  18  to form the balloon check valve  168 . The balloon check valve  168  can seal the cervical canal and the uterine cavity  176  from the inner catheter lumen  10 . The reproductive materials  166  can remain in the uterine cavity  176  without being expelled through the cervix. 
       FIGS.  12 A to  12 E  illustrate of an everting catheter for performing an IUD placement procedure.  FIG.  12 A  shows an everting catheter with an IUD contained in an everting catheter system  2  in the inverted membrane position. Everting membrane and IUD (not visible in this figure) are contained within outer catheter  4  with acorn tip  242  at the distal end. Acorn tip  242  can have an opening at the distal end (not visible). On the proximal end of outer catheter  4  there is a t-fitting or Y-fitting  244  which contains an x-ring gasket (not visible). Extension tubing and stopcock  248  supplies inflation or hydraulic energy to the everting catheter system. Hydraulic energy can be supplied by saline, air, a combination of saline and air, or gases such as CO2, contrast media, culture media, and other fluids. In operation, hydraulic energy can be in the range of 2 to 4 atmospheres, or 1 to 6 atmospheres. Inner catheter  8  is translatable within the outer catheter  4  to advance and retract the everting membrane (not visible) On the proximal end of the inner catheter  8  there is a proximal hub  246  that is designed to allow passage of the IUD suture  252 . Other embodiments may not require the IUD suture to be exposed from the inner catheter. 
       FIG.  12 B  shows the distal end of the everting catheter with IUD  254  visible in the everted membrane which is only partially everted from acorn tip  242 . IUD  254  can be in a collapsed condition within the membrane  6 . IUD suture  252  can be proximal to the IUD  254 . The IUD suture  252  can be within the central lumen of inner catheter  8 . IUD  254  can have rounded distal ends  256  and stem  258 . IUD  254  can have radio-opaque marker band  260 , copper or drug or hormone eluting section  262 , and other features. 
       FIG.  12 C  shows the advancement of the everting membrane  6  pulling IUD  254  through the distal end of outer catheter  4  and opening on acorn tip  242 . Eversion of the membrane can be performed in response to hydraulic energy or pressure within the everting catheter system  2  through the inflation tubing and stopcock (not shown). The everting membrane  6  responds to hydraulic energy to roll inside out. The advancement of the everting membrane  6  can be performed by the user translating the inner catheter (not visible) or automatically in response to the hydraulic energy. The everting membrane can be dimensioned in a range of 1 mm to 5 mm in diameter for the endocervical canal or 4.0 to 4.5 mm in outer diameter when pressurized to 2 atmospheres. The everting membrane can have an outer diameter range of 2 mm to 7 mm, with a wall thickness of 0.001″ to 0.004″, or 0.0015″. The everting membrane can be manufactured from irradiated polyolefin, polyurethane, Pebax, silicone, or other flexible membrane material. The everting membrane wall thickness could have a range of 0.002″ to 0.010″ depending upon the modulus of the membrane material. 
       FIG.  12 D  shows the distal end of the outer catheter  4  and acorn tip  242  with everting membrane  6  in a further stage of eversion advancing IUD  254  through the distal end opening in acorn tip  242 . Rounded ends  256  of IUD  254  are in the initial stages of returning to its natural state as opposed to its collapsed state. In its natural state, IUD  254  can have a “T” or “Y” shape although other shapes and configurations are possible for intrauterine devices. 
       FIG.  12 E  shows the completion of the eversion process with everting membrane  6  advanced further beyond the acorn tip  242  and fully exposing IUD  254  that can now be in its natural (i.e., unbiased or mechanically relaxed) state or “T” shape. Stem  258  and hormone or drug eluting section  262  are fully exposed from the distal end of membrane  6 . Certain. IUDs are equipped with bands or rings of copper material as a spermicidal agent. IUD suture  252  can still be within the central lumen of membrane  6  and inner catheter (not visible). At full exposure outside of membrane  6 , IUD  254  can be at the insertion depth within the uterine cavity. The insertion depth of the IUD  254  within the uterine cavity can be determined or prescribed by the length of the membrane  6 , the amount of eversion performed by the user during the translation of the inner catheter  8 , which can vary depending upon the desired depth of insertion. In addition, the outer catheter  4  can be configured with telescoping tubes (not shown) that can change the membrane length and the insertion depth within the uterine cavity. 
       FIGS.  13 A to  13 I  illustrate additional derivations for an everting catheter system  2  for IUD placement.  FIG.  13 A  shows everting catheter system  2  with IUD  254  in a collapsed state within the everting membrane  6  (not visible) within outer catheter  4 . Inner catheter  8  can be proximal to Y-fitting  244  and continues within outer catheter  4 . Everting membrane  6  can be connected to the distal end of inner catheter  8  and to the distal end of outer catheter  4 . Acorn tip  242  can be located at the distal end of outer catheter  4 . Everting membrane  6  can be pressurized by fluid, gas, or a combination of both through extension tubing and stopcock  248 . Within inner catheter  8  can be pusher  264  which can be proximal to inner catheter hub  246 . Pusher  264  can be a hollow tube with pusher hub  266  that can contain IUD suture  252  within its inner lumen. 
       FIG.  13 B  shows in a side view acorn tip  242  with dashed lines indicating through lumen  276  within the acorn tip. Acorn tip  242  can be used to seat the everting catheter system  2  at the exocervix of the patient. Acorn tip  242  contains intubation tip  268  on the posterior surface that can be designed to gain purchase or intubate the opening of cervix with a rounded surface  269  on the anterior portion. Acorn tip  242  can have outer shoulders  270  to provide a stopping mechanism to avoid inadvertent insertion of the outer catheter  4  within the cervical canal of the patient. Distal end opening  272  can be configured to allow the everting membrane deliver the IUD (both not shown). 
       FIGS.  13 C and  13 D  show another type of acorn tip  242  with lower profile anterior surface  274  with outer shoulders  270  that are reduced in the anterior portion of circumference of acorn tip  242 . Lower profile anterior surface  274  provides the physician greater viewing angle of the exocervix when placing the everting catheter (not shown). The lower profile anterior surface can be used by the physician to gain better visualization of the exocervix while maintaining the functions of the acorn tip in regards to intubating the exocervix, gaining purchase, and providing a stopping mechanism from inadvertent advancement of the outer catheter into the cervical canal. Alternative acorn tip  242  contains an intubation tip  268  on its distal end on the posterior surface to facilitate initial device placement at the exocervix of the patient with ramp  271  leading to shoulder  270 . Dashed lines indicate through lumen  276  with distal end opening  272 . 
     Returning back to an alternative embodiment of everting catheter system  2 ,  FIG.  13 E  shows IUD  254  being advanced by everting membrane  6  in response to the advancement of inner catheter  8  within outer catheter  4  using hydraulic energy supplied in extension tubing and stopcock  248 . In conjunction, pusher  264  can advance with everting membrane  6  with two strands of IUD suture  252  exiting pusher hub  266 . 
       FIG.  13 F  shows further advancement of IUD  254  with everting membrane  6  and translation of inner catheter  8  within outer catheter  4 . Rounded ends  256  are exposed distal at the end of the everting membrane  6  as the membrane everts inside out and pulls the IUD forward. 
       FIG.  13 G  shows IUD  254  released from everting membrane  6  with IUD fully in its natural state or “T” or “Y” shape. IUD suture  252  can be proximal to the IUD and runs through everting membrane  6 , pusher  264 , and inner catheter (not visible). To complete IUD release, pusher  264  advances IUD  254  beyond the distal end of everting membrane  6 . 
       FIGS.  13 H and  13 I  illustrate alternative embodiments of the distal end of pusher  264 .  FIG.  13 H  shows distal end of pusher  264  with pusher cup  278  with concave opening  280  to accept and hold the profile of the proximal end of IUD  254  (not shown). Pusher  264  can have through lumen with central axis  282 . Distal end pusher cup  278  facilitates the handling and loading of IUD  254  within an everting catheter (not shown). 
       FIG.  13 I  shows an alternative form of distal end of pusher  264  with through lumen and central axis  282  and with a split tube opening  284  at the distal end. Split tube opening  284  can be configured to open and accept and hold the proximal end of IUD  254  (not shown). Distal end split tube opening  284  facilitates the handling and loading of IUD  254  within an everting catheter (not shown). 
       FIGS.  14 A and  14 D  illustrate the advancement of IUD  254  within an everting membrane  6  from the collapsed state to the release of IUD  254  and return to its natural state or “T” shape.  FIG.  14 A  shows the everting membrane  6  advancing through acorn tip  242  pulling IUD  254  in a collapsed, low profile state within an everting catheter system  2 . Round ends  256  are compressed by the everting membrane  6  in response to the hydraulic energy supplied through extension tubing and stopcock (not visible). 
       FIGS.  14 B and  14 C  further illustrate the advancement of IUD  254  within an everting membrane  6  within an everting catheter system  2 . As IUD  254  is pulled forward by the everting membrane, IUD  254  can return to its natural state or a “T” or “Y” shape.  FIG.  14 B  shows the everting membrane  6  in a pressurized state via hydraulic energy. IUD suture  252  can be contained within the distal end of pusher  264  within split opening  284 . 
       FIG.  14 D  illustrates another embodiment of everting catheter system  2  in which the hydraulic energy can be removed by a pressure source  286  via extension tubing and stopcock  248 . Once hydraulic energy is removed from everting catheter system  2 , everting membrane  6  can no longer grip IUD  254  and pusher  264  can advance the proximal end of IUD beyond the distal opening of everting membrane. Pressure source  286  an be an inflation device as shown or other devices such as a syringe, a syringe and compliant tube, a pump, or a pressurized cannister or container. 
       FIG.  15 A  illustrates everting catheter system  2  equipped with a one-handed delivery mechanism. On the proximal end of everting catheter system  2 , housing  288  can be configured with rolling wheel  290  and outer catheter release button  292 . At the distal end, acorn tip  242  can be designed to engage the exocervix when placed in the patient for IUD delivery and placement. IUD  254  can be visible within outer catheter  4 . Extension tubing and stopcock  248  can be located on the posterior portion of housing  288 . Exiting the proximal portion of housing  288 , pusher  264  and pusher hub  266  can be visible with IUD suture  252  protruding the through lumen of pusher  264 . 
       FIG.  15 B  demonstrates the one-handed operating mechanism of everting catheter system  2  using housing  288 . The operator&#39;s thumb can be placed on rolling wheel  290  with outer catheter release button  292  in close proximity. IUD  254  can be visible within outer catheter  4  and pusher  264  with pusher hub  266  can be visible exiting the proximal portion of the housing. 
       FIG.  15 C  shows a top view of the one-handed mechanism of everting catheter system  2  in which the inner catheter  8  can be visible in housing  288 . Also visible are inner catheter hub  246  with pusher  264  protruding from the proximal portion of the inner catheter hub. IUD suture  252  can be visible protruding from the proximal opening of pusher hub  266 . Also visible within housing  288  can be pusher stop  294  and gear wheel housing  296  under the thumb of the operator. 
       FIG.  15 D  illustrates further in a top view the one-handed operation of everting catheter system  2  during the advancement of everting membrane  6  puling IUD  254  through acorn tip  242 . Rolling wheel  290  (partially visible under the thumb of the operator) can be used to advance inner catheter  8  which allows the everting membrane to advance. Advancement of the everting membrane  6  can be limited when inner catheter hub  246  reaches gear wheel housing  296 . As the inner catheter  8  can be advanced into the outer catheter  4 , inner catheter hub  246  reaches gear wheel housing  296  and advances pusher  264  until pusher hub  266  mechanically engages pusher stop  294 . In operation, the operator will actuate outer catheter release button  292  that will allow the outer catheter  4  and attached everting membrane  6  to retract while pusher  264  maintains in place in relation to housing  288  with pusher stop  294 . The distal end of pusher  264  thereby advances IUD  254  out of the distal end of everting membrane  6  and releasing IUD  254  in the uterine cavity. In operation, the operator will remove the entire everting catheter system  2  and having the IUD suture  252  threading out of pusher  264 . 
       FIGS.  16 A to  16 J  illustrate another embodiment of everting catheter system  2  with handle  30 . Protruding distal to handle  600  can be outer catheter  4  and protruding proximal to the handle can be pusher  264  with IUD sutures  252  exiting the pusher hub  266 . On the anterior portion of handle  600  can be inner catheter button  298  and outer catheter release button  292 . Protruding on the posterior portion of handle  600  can be extension tubing and stopcock  248  (partially visible). 
       FIG.  16 B  shows inner catheter button  298  being advanced within housing slot  308  on the anterior surface of housing  288 . Inner catheter button  298  is attached to the proximal end of inner catheter (not shown) and its advancement translates the inner catheter and everting membrane to deliver an IUD (not shown). In operation, inner catheter button  298  advances until it engages outer catheter release button  292  also on the anterior surface of housing  288 . 
       FIG.  16 C  shows the retraction of outer catheter release button  292  which performs the release of the IUD from the everting catheter (not shown). 
       FIG.  16 D  provides information on how housing  288  works with everting catheter system  2  to perform the advancement and release of the IUD (not shown). In  FIG.  16 D , the anterior portion of housing  288  is removed showing the interior portions of the everting catheter system  2  including inner catheter hub  246 . Alternatively, inner catheter hub  246  can be eliminated by inner catheter button  298  or have both devices as shown. Also visible is pusher  264  and pusher hub  266  with IUD sutures  252  exiting the proximal portion of the pusher hub. Outer catheter release button  292  and inner catheter button  298  is also visible and at this position, the advancement of the everting membrane (not shown) is complete. Contained within the posterior portion of housing  288  are inflation tubing slot  300  and pusher engagement tabs  302  which is configured to mechanically hold pusher hub  266  at the completion of the eversion step. Also visible are housing holes  304  that are designed to snap the anterior and posterior sections of housing  288 . 
       FIG.  16 E  shows a cut-away view of the proximal portion of Y-fitting  244  with inner catheter  8  exiting the proximal of the Y-fitting. Extension tubing and stopcock  248  (stopcock not shown) is exiting posteriorly from Y-fitting  244  and through housing  288  through inflation tubing slot  300 . Outer tubing release button  292  is mechanically attached to Y-fitting  244  and can be retracted in housing  288  along inflation tubing slot  300 . 
       FIG.  16 F  shows the inflation tubing slot  300  on the posterior surface of housing  288  in another cut-away view. Extension tubing and stopcock  248  (stopcock not shown) is visible in inflation tubing slot  300 . 
       FIG.  16 G  shows a cut-away view of the proximal portion of housing  288  and proximal hole  306 . Cut away view of pusher  264  is visible exiting from the proximal portion of inner catheter hub  246 . The internal track of the pusher engagement tabs  302  that progressively gets narrower as it extends from the proximal portion of housing  288  to the distal portion is visible on the internal posterior surface of housing  288 . Pusher hub  266  can have a conical or tapered profile on its distal portion to travel through the pusher engagement tabs  302 . The flat proximal portion of pusher hub  266  can serve as a mechanical detent in the proximal direction once the pusher hub  266  extends beyond the pusher engagement tabs  302 . 
       FIG.  16 H  shows the initial step of IUD delivery and placement with another cut-away view of the right-hand side of housing  288  with outer catheter  4  distal to Y-fitting  244  and attached to outer catheter release button  292 . Also, on the anterior surface of the housing and in housing slot  308  is inner catheter button  298 . Exiting proximal to inner catheter  8  and inner catheter button is pusher  264 . Attached to the proximal end of pusher  264  is the pusher hub  266  with through lumen for IUD sutures  252 . 
       FIG.  16 I  shows in the same cut away view the range of advancement of inner catheter button  298  during the eversion step with everting catheter system  2  hydraulically pressurized through extension tubing and stopcock  248  (stopcock not shown). This embodiment shows an advancement of the inner catheter  8  within outer catheter  4  of 12.6 cm. This distance of advancement corresponds to an insertion depth within the uterine cavity of 6.3 cm. Other lengths of advancement are possible from 3 cm to 24 cm. In addition, the depth of insertion can be under the physician&#39;s control by stopping the eversion step at any point during the process. 
       FIG.  16 J  shows the release step of the IUD delivery process with everting catheter system  2  in which outer catheter release button  292  is retracted bringing pusher  264  through inner catheter  8  to advance the IUD (not shown) through the everting membrane (not shown). 
       FIGS.  17 A to  17 I  illustrate further embodiments of an everting catheter that delivers an IUD.  FIG.  17 A  shows everting catheter system  2  with housing  288  with pusher  264  and pusher luer hub  310  exiting proximal to the housing. Pusher luer hub  310  is configured to accept a syringe  74  or other irrigation source to provide fluid, saline, contrast media, sonographic media, drugs or therapeutic agents, or a gas or air through the central lumen of everting catheter system  2 . Irrigation fluid or media can facilitate visual identification of the exocervix or the uterine cavity with ultrasonography or fluoroscopy. 
       FIG.  17 B  shows everting catheter system  2  at the initial stage of the eversion process with anterior portion of housing  288  removed for identification of internal parts and mechanisms. 
       FIG.  17 C  shows everting catheter system  2  with hydraulic energy is supplied through extension tubing and stopcock  248 . Inner catheter button  298  is advanced to translate inner catheter  8  within outer catheter  4 . Everting membrane  6  exits distal to acorn tip  242  and pulls IUD (not shown) and pusher  264  through the central lumen of everting catheter system  2 . Pusher luer hub  310  is translated through proximal hole  306  of housing  288  and into the track of pusher engagement tabs  302 . 
       FIG.  17 D  shows the next step of the eversion process with inner catheter button  298  engaging outer catheter release button  292  and pusher luer hub  310  reaching mechanical detent of pusher engagement tabs  302 . 
       FIG.  17 E  shows the next step in the IUD delivery process with syringe  74  connected to extension tubing and stopcock  248  to draw negative pressure within everting catheter system  2 . Negative pressure withdraws the hydraulic energy in the everting membrane  6 . 
       FIG.  17 F  shows the next step in the IUD delivery process with outer catheter release button  292  retracted and thereby retracting the outer catheter  4 , everting membrane  6 , and inner catheter  8  while maintaining the position of the pusher  264  relative to the housing  288 . Pusher engagement tabs  302  prevent the pusher luer hub  310  from retracting and thereby maintaining the position relative to the housing  288 . 
       FIG.  17 G  shows a close-up photograph of the distal end of the everting membrane  6  with hydraulic energy removed from everting catheter system  2  and with distal end of pusher  264  extending beyond the distal opening of the everting membrane  6 . Split tube opening  284  is at the distal end of pusher  264  and illustrates that the distal end of pusher  264  can exit everting membrane  6 . 
       FIG.  17 H  shows an alternative type of syringe  74  with plunger spring  314  on plunger  76 . Engagement button  312  can translate within syringe housing  208  to lock onto ridges  316  on multiple locations on plunger  76 . When depressed, engagement button  312  can lock plunger spring  314  in a compressed condition. 
       FIG.  17 I  shows syringe  74  with engagement button  312  released allowing plunger spring  314  to expand and retract plunger  76  back to provide negative pressure within syringe  74  and an everting catheter system  2  (not shown). 
       FIGS.  18 A through  18 C  illustrate another embodiment of everting catheter system  2  that automatically provides negative pressure to remove hydraulic energy in the everting catheter at the step of releasing the IUD (not shown) during the delivery and placement procedure.  FIG.  18 A  shows everting catheter system  2  with housing  288  and syringe  74  mounted or attached to the bottom posterior surface of the housing. Syringe  74  can have plunger spring  314  compressed and engagement button  312  locked into syringe housing  208 . Syringe  74  is connected via inflation tubing  318  as a conduit for the hydraulic energy within everting catheter system  2 . 
       FIG.  18 B  shows the advancement of inner catheter button  298  in housing slot  308 . Advancement of inner catheter button  298  translates inner catheter (not shown) within outer catheter  4  and advancing everting membrane and IUD (both not shown). 
       FIG.  18 C  shows the next step in the IUD delivery and placement process. The depression of outer catheter release button  292  forces engagement button  312  to release plunger spring  314  and plunger  76  to create negative pressure in the everting catheter system  2  via inflation tubing  318 . At this point the outer catheter release button can be retracted back along housing slot  308  to retract the outer catheter  4 , everting membrane and inner catheter (not shown) while maintaining the position of pusher (not shown) and releasing the IUD from the everting membrane (both not shown). 
       FIG.  19 A  illustrates an everting catheter system  2  for delivering an IUD in the inverted state. IUD  254  can be loaded in a collapsed condition within balloon membrane (not visible) and inner catheter  8 . Inner catheter  8  can be within outer catheter  4 . At the distal end of outer catheter  4 , moveable flange can be a marker for insertion depth with indicia  402 . The proximal end of outer catheter  4  there is a t-fitting  244  for pressurization of the everting balloon with x-ring valve (not shown) for the translation of inner catheter  8 . Inner catheter  8  has proximal hub  246  that can be a luer connector, knob, or handle for the manipulation of inner catheter. Within the central lumen of inner catheter  8  is pusher  264  with lumen for IUD suture(s)  252 . Pressurization of everting catheter system  2  can be performed by syringe  410  and syringe plunger  409  that can be connected by the user or physician to connector  413  that can be connected to compliant tube  412 . Pinch clamp  411  can be used by the user or physician to close compliant tube  412  to maintain pressure within the everting balloon. Once pressurized, syringe  410  can be disconnected and removed from the everting catheter system  2  prior to insertion within the patient. 
       FIGS.  19 B to  19 D  are close-up views of different sections of everting catheter system  2 .  FIG.  19 B  is a close-up view of the distal end of outer catheter  4  with the initial portion of everting balloon  6  visible exiting the distal end outer catheter  4 . The distal end opening of outer catheter  4  have an acorn tip or no acorn tip and a smooth, rounded, low profile distal tip. The distal end can have indicia  402  which denote 7 cm, 8 cm, 9 cm, and 10 cm markings for example, for showing the user (e.g., physician) an indication of insertion depth. Moveable flange  401  can be placed by the user (e.g., physician) to provide a visible and tactile indicator for insertion depth. Visible within outer catheter  4  can be IUD  254  in a collapsed, loaded, low profile state within the everting balloon and inner catheter (not visible). 
       FIG.  19 C  is a close-up view of the pressurization system for everting catheter system  2 . Pressurization of the everting catheter  2  can be performed by syringe  410  filled with saline, sterile water, air, or an inert gas, or combination of gases and fluid media. Depression of syringe plunger  409  by the user or physician supplies hydraulic energy to the everting balloon. Syringe  409  can have a volume of 1 cc, 3 cc, 5 cc, or 10 cc, for example, 3 cc as shown. Other volumes are possible. Pressurization of the everting catheter system  2  can distend compliant tube  412 . Compliant tube  412  can be made from silicone and/or other elastomeric materials, such as polyurethane, rubber, and TPE, or combinations thereof. Compliant tube  412  can maintain a near constant pressure within everting catheter system  2  during inversion and eversion. Compliant tube  412  can provide a mitigation from the user or physician inadvertently putting in too much pressure within the everting catheter system  2  since the silicone tube can continue to distend in response to the added hydraulic pressure. Pressurization amount can 1 to 4 atmospheres with 2 atmospheres as a nominal level. The amount of compliance within the silicone tube can depend upon the durometer of the material, the wall thickness of the tube, and the length of the tube available for distension. As shown for example, compliant tube  412  can be silicone with a durometer of 50 A, 6 cm in length, with an outer diameter of 4.75 mm and wall thickness of 1 mm. The pressurization system can be closed by the user with pinch clamp  411 , for example to close the internal lumen of compliant tube  412  once pressurized by syringe  410 . Other tubing closure devices can be used, such as stopcocks, gate valves, roller clamps, or combinations thereof. A one-way check valve or a luer-activated valve can be on complaint tube  412  instead of or in combination with connector  413  to allow for one-way pressurization without requiring the user to actuate a closure device to close and maintain pressure within compliant tube  412  and everting catheter system  2 . Hydraulic pressure supplied by syringe  410  and syringe plunger  409  can be in fluid communication with everting catheter system  2  through t-fitting  244  with x-ring valve (not shown) maintaining pressure during eversion of balloon membrane and the translation of inner catheter  8  within outer catheter  4 . Inner catheter  8  can be made from nylon, Pebax, polypropylene, polyethylene, or combinations thereof. Inner catheter  8  can extend from the distal end of the fully everted balloon to the proximal end of t-fitting  244  with an outer diameter of 4 mm and an inner diameter of 3 mm. 
       FIG.  19 D  is a close-up view of the proximal portion of everting catheter system  2  and illustrates inner catheter  8  with proximal connector hub  246  with central through hole. Within the central through hole can be pusher  264  with pusher hub  266  with central through hole with IUD sutures  252 . Proximal connector hub  246  and pusher hub  266  can be luer connectors to allow for the connection of syringes or tubing for the injection of fluid, saline, or gas media for distention of the uterine cavity for ultrasound, fluoroscopic, or endoscopic visualization. Proximal connector hub  246  and pusher hub  266  can be handles or knobs for manipulation of the catheters by the user or physician. Pusher  264  can be made from nylon, Pebax, polypropylene, polyethylene, or combinations thereof. Pusher  264  tubing can have an outer diameter of 2 mm and inner diameter of 1.25 mm and a length that approximates the entire length of everting catheter system  2 , for example, to allow the user or physician to expel the IUD from inner catheter  8  during placement within the uterine cavity. 
       FIG.  20 A  illustrates the everting catheter system  2  after full eversion of the balloon in the process of delivering an IUD. IUD  254  can be in a collapsed, loader state within inner catheter  8  and everting balloon  6 . Outer catheter  4  can contain indicia markings  402  and depth insertion marker flange  401 . Outer catheter  4  can be connected to t-fitting  244  with x-ring valve (not shown) and can be connected to compliant tube  412  with luer connector  413  and tubing pinch clamp  411  for hydraulic pressurization of everting catheter system  2 . Immediately proximal to t-fitting  244  can be proximal connector hub  248  denoting full eversion of the everting balloon and full translation of inner catheter (not visible). Proximal to the proximal connector hub  248  is pusher  264  and pusher hub  266 . Proximal to pusher hub  266  can be IUD sutures  252  seen beyond the central lumen of the tubing. 
       FIG.  20 B  is a close-up view of the distal end of the everting catheter system  2  with fully everted balloon  6  and IUD  254 . Distal end of inner catheter (not visible) can be connected to everting balloon  6  and rounded distal ends  256  of IUD  254  can be immediately distal to the fully everted balloon  6 . Visible through the everted balloon  6  and inner catheter can be portions of IUD  254  including copper wire  271 , IUD stem hole  272 , suture knot  273  and IUD sutures (not visible). Everting balloon  6  can be connected to outer catheter  4  with indicia markings  402 . For example, everting balloon  6  can be 6 cm long to traverse the length of the cervix and which can be 3.5 cm in length from the exocervix to the internal cervical os. Different lengths of everting balloon  6  can be used to approximate the uterine lengths of different patients. Everting balloon can, for example, have an outer diameter of 4 mm in the pressurized state of 2 atmospheres and a wall thickness of 0.0015″ thousandths of an inch. Everting balloon can be made from irradiated polyolefin, polyethylene, Pebax, polyurethane, other biocompatible materials that can create a hydraulic everting balloon, or combinations thereof. 
     Distal end of inner catheter (not visible) can have an internal diameter that, for example, can allow for the collapsed IUD to fit within the tubing For example, an internal diameter of 3 mm can allow the collapsed IUD to fit within the tubing but keep the rounded distal ends  256  protruding distal to the inner catheter (not visible) and the everting balloon  6 . Distal end of pusher (not visible) can be just proximal to IUD stem hole  272  and suture knot  273 . Distal end opening of everting balloon  6  can be connected to the distal end of the inner catheter (not visible). When inverted and pressurized, everting balloon  6  can collapse IUD  254  in a lower profile state that facilitates advancement through the cervical canal and into the uterine cavity. When inverted and pressurized, everting balloon  6  can collapse and compress the rounded distal ends  256  together to a low profile, for example, for advancement through the everting catheter system  2 , the distal end opening of the outer catheter  4 , and the cervical canal and into the uterine cavity. 
       FIG.  20 C  is a close-up view of the proximal portion of the everting catheter system  2  after full eversion in the process of delivering an IUD  254 . Outer catheter  4  can be connected to t-fitting  244  with x-ring (not visible) and is fluidly coupled to compliant tube  412  with tubing pinch clamp  411  shown in the closed condition with hydraulic pressurization within the everting catheter system  2 . Proximal connector hub  248  can be seen immediately proximal to t-fitting  244 , for example, denoting full eversion of the everting balloon (not shown) and full translation of the inner catheter (not visible). Within proximal connector hub  248  can be pusher  264  with pusher hub  266  on its proximal end with IUD sutures  252  seen exiting through the central lumen of pusher  264 . 
       FIGS.  21 A to  21 C  illustrate the process of delivering an IUD within a simulated uterine cavity model  500  (standing in for a patient&#39;s uterine cavity and other respective anatomy for illustrative purposes) with metric scale  510  provided for reference.  FIG.  21 A  illustrates the placement of IUD  254  within simulated uterine cavity model  500  with fundal portion  501  which simulates the cranial apex of the uterine cavity, and cornual regions  502  (denoting the patient&#39;s right fallopian tube os) and  503  (denoting the patient&#39;s left fallopian tube os). Simulated uterine cavity model can contain lower uterine segment  504  with simulated cervical canal  505  and simulated exocervix  506 . Everting catheter system  2  can have everted balloon  6  fully everted with rounded distal ends  256  of IUD  254  approximating the fundus  501  of the uterine cavity and distal to the everted balloon  6 . Pusher  264  can be proximal to IUD  254 . Flange  401  can abut the exocervix  506  with an insertion depth of approximately 9 cm, for example. 
       FIG.  21 B  illustrates a next (e.g., intermediate) step in the process of IUD placement with everting catheter system  2 . Everting catheter system  2  can be retracted 1.5 cm as seen by flange  401  now being a distance, for example, of 1.5 cm from exocervix  506 . In combination, IUD  254  can be expelled from the distal end of everting balloon  6  with pusher  264  and retraction of everting catheter system  2 . IUD  254  can have rounded distal ends  256  extending outward towards cornual regions  502  and  503 . 
       FIG.  21 C  illustrates a next (e.g., final) step of IUD  254  placement with the everting catheter system (not shown) that can be completely removed from simulated uterine cavity model  500 . Rounded distal ends  256  can remain in the cornual regions  502  and  503 . IUD sutures  252  can be visible exiting the exocervix  506 . The user or physician can trim the excess length of IUD sutures  252  depending upon the amount of excess IUD suture or type of IUD. 
       FIGS.  22 A to  22 E  illustrate a packaging configuration for the transit and loading of the everting catheter system  2  for delivering an IUD. Everting catheter system  2  can be placed onto pouch card  600  in the fully everted position with IUD  254  at the distal end of the everting balloon (not visible). Pouch card  600  and everting catheter system  2  can be placed into a sealed pouch (not shown) for sterilization, shipping, and eventual usage by a physician. Pouch card  600  can be made from clean laminated paper card stock, PETG, polypropylene, polyvinyl chloride, PET, or combinations thereof. Affixed to pouch card  600  can be protective tube  601  which can be, for example, 6.5 cm in length with an ID of 4 mm. Protective tube  601  can be sized in length to fit over the fully everted balloon (not visible) and leave IUD  254  in the open configuration with rounded distal ends  256  beyond the distal end of the protective tube  601 . Protective tube  601  internal diameter can be sized to allow a non-pressurized everting balloon (not visible) to slide through the central lumen. When everting balloon (not visible) is pressurized, everting balloon outer diameter can contact the internal lumen of protective tube  601 . Contacting the internal lumen when pressurized can, for example, allow the user or physician to easily retract the everting balloon and inner catheter for loading and preparation for use. Protective tube  601  can be made from nylon but can be made from polypropylene, PET, Pebax, and other tubing materials used in medical device packaging. T-fitting  244  and proximal connector hub (not visible) can be held in place by pouch tabs  602  with inner catheter (not visible) fully translated into outer catheter  4 . Pusher  264 , pusher hub  266 , and IUD sutures  252  can extend proximal to everting catheter system  2 . 
       FIG.  22 B  is a close-up view of a variation of the distal portion of pouch card  600  and protective tube  601  with everting balloon (not visible) fully everted within protective tube  601 . IUD  254  can be in an open configuration and can be positioned at the distal end of everting catheter system  2  with IUD sutures (not visible in this view) running through the entire length of the inner catheter and pusher of everting catheter system  2 . Proximal end of protective tube  601  can be intubated by the distal end of outer catheter  4 . 
       FIG.  22 C  illustrates a step (e.g., unpacking, assembling, and pressurizing) in the preparation of everting catheter system  2 . Pouch  603  can be peeled back halfway to expose the proximal portion of pouch card  600 . The user or physician can connect syringe  410  to compliant tube  412  with pinch clamp  411  in the open position. The compliant tube can be rotated upwards or perpendicular to the surface or pouch card  600 . The everting catheter system can be pressurized with 3 cc of saline. 
       FIG.  22 D  shows the compliant tube  412  pressurized with pinch clamp  411  can be in the closed position with syringe disconnected and removed from luer connector  413 . IUD sutures  252  can then pulled to retract IUD  254  within the distal end of the inner catheter (not visible) within protective tube  601 . 
       FIG.  22 E  is a close-up view of the distal portion of pouch card  600  with the IUD  254  that can be in the collapsed and loaded configuration inside the inner catheter (not visible) within protective tube  601 . The everting balloon (not visible) can then be fully inverted with inner catheter (not visible) that can be fully translated back, for example, to remove the everting catheter system  2  from the protective tube  601  and pouch  603  in preparation for insertion into the patient. 
     Any elements described herein as singular can be pluralized (i.e., anything described as “one” can be more than one). Any species element of a genus element can have the characteristics or elements of any other species element of that genus. The media delivered herein can be any of the fluids (e.g., liquid, gas, or combinations thereof) described herein. The patents and patent applications cited herein are all incorporated by reference herein in their entireties. Some elements may be absent from individual figures for reasons of illustrative clarity. The above-described configurations, elements or complete assemblies and methods and their elements for carrying out the disclosure, and variations of aspects of the disclosure can be combined and modified with each other in any combination. All devices, apparatuses, systems, and methods described herein can be used for medical (e.g., diagnostic, therapeutic or rehabilitative) or non-medical purposes. 
     U.S. Pat. No. 9,028,401, issued May 12, 2015; U.S. Pat. No. 9,101,391, issued Aug. 11, 2015; and U.S. Pat. No. 10,034,986, issued Jul 31, 2018; and U.S. Published Application Nos. 2019/0009058, published Jan. 10, 2019; 2020/0206463, published Jul. 2, 2020; 2020/0297384, published Sep. 24, 2020; and 2020/0023162, published Jan. 23, 2020 which are all incorporated by reference herein in their entireties. 
     Any elements described herein as singular can be pluralized (i.e., anything described as “one” can be more than one). Any species element of a genus element can have the characteristics or elements of any other species element of that genus. “Dilation” and “dilatation” are used interchangeably herein. The media  155  delivered herein can be any of the fluids (e.g., liquid, gas, or combinations thereof) described herein. The patents and patent applications cited herein are all incorporated by reference herein in their entireties. Some elements may be absent from individual figures for reasons of illustrative clarity. The above-described configurations, elements or complete assemblies and methods and their elements for carrying out the disclosure, and variations of aspects of the disclosure can be combined and modified with each other in any combination. All devices, apparatuses, systems, and methods described herein can be used for medical (e.g., diagnostic, therapeutic or rehabilitative) or non-medical purposes.