Patent Application
20140051968
The present invention relates to endorectal balloons that are used for immobilizing the region surrounding the prostate during pre-treatment simulation and target localization, as well as during the delivery of radiation therapy to treat prostate cancer. More particularly, the present invention relates to balloon specially designed to have a pocket for holding data cable therein. The data cable can be for any types of sensor, and preferably is a non-implantable electromagnetic rectal sensors that can accurately monitor the movement during a radiation therapy, or a non-implantable plastic scintillator dosage sensor that can monitor dosimetry during therapy.
Treatment of prostate cancer using radiation therapy is difficult due to the prostate's position near radiation-sensitive tissues and is further complicated by surprising levels of prostate motion.
During external beam radiation therapy (XRT), radiation is directed along different axes to the target prostate, which is near the rectal wall. Where the beams cross, the radiation dose is the highest, and thus the prostate can be preferentially targeted. Misdirected radiation beams may perforate the rectal wall causing radiation proctitus (rectal bleeding), as well as erectile dysfunction (ED), incontinence and other complications. In fact, as many as half the treated men suffer from ED and/or incontinence.
A major factor limiting radiation oncologists' attempts to reduce the volume of the anterior rectal wall and other healthy tissues receiving a high radiation dose is the position of the prostate gland as well as the intrinsic motion up to 10 mm in the anterior to posterior direction caused by rectal peristalsis. Accordingly, oncologists generally will add a margin to the radiation field in order to ensure that the entire prostate gland receives the prescription dose. This margin is typically on the order of 5 to 15 mm. As a consequence, lower doses of radiation may need to be used so as not to overexpose healthy structures. However, this may lead to inadequate radiation treatment and a higher probability of local cancer recurrence.
US20030028097 by MedRad describes an rectal balloon to help immobilize the prostate during treatment. One of the problems with the MedRad design is the discomfort associated with installing the rectal balloon within the rectal cavity. In particular, a relatively sturdy and wide diameter shaft is connected to a relatively large thick-walled balloon. Because the balloon is not supported by anything other than by the shaft, the balloon is formed of a relatively rugged and thick material. The resulting relatively large size and stiffness of the balloon causes considerable discomfort for the patient.
A second, and more important, problem with the MedRad rectal balloon is that it is “non-conforming.” Thus, when squeezed, the shape of the balloon is lost, because there are no interior welds restraining the balloon. Thus, even if shaped when lightly inflated, the shape is lost when squeezed or when placed in the constrained environment of the rectum. Thus, the prostate can easily slide off its surface, and the balloon does not sufficiently immobilize the prostate.
Because of these problems, a need arose for a rectal balloon that retains the prostate in a fixed position when the balloon is in a fully inflated and/or squeezed or constrained condition. A balloon that can retain a shape, even when squeezed or otherwise constrained, is known as a “conforming” balloon.
U.S. Pat. No. 8,080,031 and related applications describe a rectal balloon that is conforming. This balloon has an interior weld that restrains the balloon such that it does not lose shape, even when squeezed in the highly mobile environment of the rectum. In more detail, the balloon is made of three layers, wherein the middle layer is connected to the top layer to provide a central groove which provides the dimpled or grooved seating area into which the prostate is wedged. The weld is shifted distally slightly, so that there is a bit more material proximal to the weld, which when overinflated stretches more, providing a proximal bulge, serving to further wedge the seminal vesicles into place.
However, there are many other ways of making a conforming balloon, and US201301009906, incorporated by reference herein, discusses a few additional such ways. For example, the restrained layer of the balloon can be welded to the central shaft or lumen, instead of a middle layer, and this would also provide a central seating area for the prostate and a conforming shape under constraint. Likewise, the surface can be pinched and welded to itself, or to a baffle, and combinations are also possible.
As discussed above, another important consideration when treating patients using radiation therapy is that the proper dose of radiation reaches the treatment site. This is very important whether the treatment method utilizes implanted radiation seeds, brachytherapy, external beams of radiation, proton particle delivery or any other form of high energy treatment. Excessive dosing of the patient can lead to severe side effects including impotence and urinary incontinence. Thus, a proper treatment plan should deliver an adequate amount of radiation to the treatment site while minimizing the dose delivered to the surrounding tissues, and it would be advantageous to the medical practitioner to know the actual dosage being delivered. and/or the position of the internal organs during radiation delivery.
U.S. Pat. No. 6,963,771 describes an implantable device for radiation dose verification. The method includes (a) placing at least one wireless implantable sensor in a first subject at a target location; (b) administering a first dose of radiation therapy into the first subject; (c) obtaining radiation data from the at least one wireless implantable sensor; and (d) calculating a radiation dose amount received by the first subject at the target location based on the radiation data obtained from the at least one wireless sensor during and/or after exposure to the first administered dose of radiation to determine and/or verify a dose amount of radiation delivered to the target location. However, the use of implantable medical devices is not an optimum solution.
U.S. Pat. No. 7,361,134 teaches a method of determining the dose by locating three or more detectors in the vicinity of a seed source of radiation. Each of the detectors provides an output indicative of the amount of radiation received from the source and complex calculations determine the location of the source from the detector outputs. However, this detector system is for brachytherapy and the detector is applied to tissue via a needle (or multiple needles), not a prostate immobilizing balloon. Further, the system cannot detect radiation in real time, and the sensor is not water equivalent.
U.S. Pat. No. 7,662,083 and U.S. Pat. No. 8,133,167 teach another sensor for brachytherapy that uses plastic scintillators coupled to optical fibers in the sensor portion. The patent does contemplate using a balloon for delivering the sensor, but no details are provided. The balloon 610 shown appears to lack any structure and be non-confirming, and therefore, would not suffice to immobilize the prostate. Additionally, the sensors and accompanying catheters need to be implanted inside a patient's body, which greatly increases the discomfort and inconvenience in practical application.
US20120068075 by Beddar provides an apparatus and methods for measuring radiation levels in vivo in real time, including a scintillating material coupled to a retention member, which could be a catheter or balloon. However, this system is highly simplistic and cannot immobilize the prostate during therapy. Indeed, the balloon 91 shown appears the same as the MedRad balloon, and can be expected to have similar shortcomings.
U.S. Pat. No. 8,183,534, also by Beddar, teaches an array of dosimeters, similar to those above, wherein the array allows a unique calibration method to be employed, as well as allowing assessment of complex, two-dimensional field patterns, such as might be encountered in IMRT and tomotherapy. However, the complex array of sensors contributes to complexity, cost and size of the device, none of which are desirable.
Therefore, there is the need for a rectal balloon that can both immobilize the prostate and be equipped with a properly positioned radiation sensor and/or motion sensor, such that the radiation dose and movement can both be monitored during treatment.
The disclosure provides an endorectal balloon that immobilizes the prostate for e.g., external beam radiation therapy, and also has pockets thereon or therein for holding a cable sensor, such as a motion and/or radiation sensor.
The balloon generally comprises a shaft having a fluid passageway extending at least partway therethrough. A balloon is affixed over an end of the shaft such that the fluid passageway communicates with an interior of the balloon. The balloon also is conforming and has a conforming depression on a top surface thereof, while the bottom surface is generally rounded to push the opposite rectal wall away from the target treatment area.
The conforming depression is made with an interior weld, and the weld can be to a middle layer, to the lumen, to itself, to a baffle, or combinations thereof. The conforming depression can be in the shape of a groove or a dimple, although a groove is currently preferred.
Co-located with the conforming depression or groove, is a pocket or channel into which a sensor can be fit. The pocket can be formed as part of the top layer weld (e.g., a U-shaped weld will form a pocket) to a middle layer or lumen, or another layer or strip can be added to make a pocket. The sensor and cable either runs through the lumen to the pocket, or can run outside the lumen to the pocket. Alternatively, or in addition, a pair of pockets can be placed on either side of the groove.
Where the sensor cable runs alongside the lumen or shaft (instead of inside it) an attachment means is also provided, e.g., a reversible locking clip or snap fit clip. This allow the sensor to be affixed to the shaft and holds the sensor in place during insertion into the rectum, yet the sensor can be removed after use and saved for the next procedure, while the balloon is disposed of.
The balloon is of course fitted with means for introducing air or other fluid such as water or contrast, and keeping the fluid therein, and these can be of any shape or design known in the art. Typical means for introducing fluids is a lumen or flexible tube with stop cock or other valve means and connector for fluidly connecting to a syringe or other air or fluid source. Alternatively, a luer lock can be used in place of stock cock and luer connector.
For rectal purposes the balloon is generally ovoid in shape, but pointed at each end like a football for easier insertion. An endorectal balloon is about 1.5×4 inches (1-2×3-4 inches) and holds about 100 ml of fluid. However, other shapes may be desired for other purposes. A single groove or dimple positioned centrally may be ideal for prostate use, since this provides a depression into which the prostate can be wedged. Furthermore, shifting the depression proximally provides more material distally than proximally, allowing more stretch on inflation, thus providing a distal bulge to stabilize the seminal vesicles and prevent prostate motion in the distal direction.
When the balloon is intended for rectal use, it can also be advantageously provided with a gas lumen that travels the complete length of the balloon, protruding from the distal end and having openings past the distal end of the balloon, thus providing a passageway for the escape of gas. Ideally, such lumen has a smooth, rounded, closed soft tip with multiple side holes for gas entry, and is positioned centrally inside the balloon, although other positions and shapes are possible. In such cases, the fluid entry lumen for inflating the balloon need not traverse the length of the balloon, but only enter the balloon at the proximal end via, e.g., a low profile inlet fitment. Nested lumens, two lumens welded together, and bifurcated lumens can also be used, so long as there is fluid connection to the inside of the balloon, and a second fluid passageway traversing the balloon, but not in fluid connection with the balloon interior, such that gas can escape therethrough. A dedicated passageway can also be provided in the lumen for the sensor, but this is not needed, and the sensor can be positioned in the air provision pathway, or even outside the lumen altogether.
The balloon is preferably made of thermoplastic elastomers (TPE), especially thermoplastic polyurethane. Other balloon fabrication materials include latex, polyethylene (PE), polypropylene (PP), silicone, vinyl, polyvinyl chloride (PVC), low density polyethylene (LDPE), polyvinylidene chloride (PVDC), linear low density polyethylene (LLDPE), polyisobutene (PIB), and poly[ethylene-vinylacetate] (EVA) copolymers, nitrile, neoprene, and the like. It is also possible to use a laminar plastic, having more than one layer, e.g., a tougher interior layer and a biocompatible or slippery outer layer.
The ideal material is a translucent, biocompatible material, that has a durometer of less than 80-100 Shore A (ASTM D2240 or ISO 868), a tensile strength of at least 3000 psi (ISO 527-3 or ASTM D882-02), a 100% modulus of 500-1000 psi (ASTM D412), an elongation at break of at least 300% (ASTM D412), and that is air tight for 30-60 minutes even under 150% stretch. In some applications, the material should also be sterilizable, without loss of its qualities such as strength, etc.
One or a more fiducial markers are placed on a surface of the balloon and/or balloon distal tip. The fiducial markers can be affixed or formed on different surfaces of the balloon. One plurality of fiducial markers may be positioned on one side of the groove and a second set may be positioned on an opposite side of the groove. One set of fiducial markers may be positioned on the top surface of the balloon and a second set of fiducial markers may be placed on the bottom surface of the balloon.
Opaque markers can be letters indicating top (T) or right (R) and left (L) sides of the balloon, or numbers or any other shape, and can be particularly advantageous for those balloons whose shape is not radially symmetrical. An end marker can also be placed on the very tip of a gas lumen, if included therein.
A stopping means may be included therewith, and is a semispherical member that is slidably mounted on the shaft, which has a curved surface facing the balloon and a locking mechanism. The shaft can also have numerical or other indicia thereon for reproducible positioning. A gas lumen can also be provided for the balloon, wherein a separate air passageway extends beyond the distal end of the balloon, preferably have a soft, flexible closed tip and two or more side holes to allow gas escape.
In one embodiment, the stopper has an upper portion, generally smoothly rounded or semispherical, which fits snugly against the anus, and a hole or groove, through which the lumen(s) is/are threaded or fit. Other shapes may be used for other body cavities, and the stopper may be optional for other cavities.
A lower locking portion of the stopper snap locks against the lumen without blocking fluid entry, and preferably has interior fins or ridges lining its hole that engage the lumen, and prevent sliding, as a locking mechanism without such ridges is prone to do. Another means of making a locking stopper is to line the interior of the hole through which the lumens are threaded with a tacky material, so that friction locks the stopper in place. Another method is to make a portion of the interior compress the lumen enough to lock it in place, but not so much as to block the lumen. A conical interior may be beneficial for this. A hinge on the locking portion allows the lock to be opened, and the lock snap fits shut.
The details of the locking mechanism can be as shown in US2010145379, incorporated herein by reference in its entirety. The upper portion of the locking stopper has a groove reaching to the central hole, so that the stopper need not be threaded over the lumen, but this groove can be replaced with a hole and thus prevent stopper loss once the valves and luer lock are added to the end of the lumen. Of course, the central hole is not necessarily round as shown in US2010145379, especially if two lumens are welded together, but should reflect the cross section of the lumen(s).
The invention includes one or more of the following embodiments, and in any combination:
The term “distal” as used herein is the end of the balloon inserted into the body cavity, while “proximal” is opposite thereto (e.g., close to the medical practitioner). The terms top and bottom are in reference to the figures only, and do not necessarily imply an orientation on usage. The length of balloon and lumen is the longitudinal axis, while a horizontal axis and vertical axis cross the longitudinal axis.
By “weld” herein we mean any method of attaching two layers of polymeric film together. Thus, the welds or attachment points can be glued, heat welded, RF welded, ultrasound welded, solvent welded, hot gas welded, freehand welded, speed tip welded, extrusion welded, contact welded, hot plate welded, high frequency welded, injection welded, friction welded, spin welded, laser welded, impulse welded or any other means known in the art.
By “central” portions herein, we are distinguishing from the edges in a bilayer construction. Thus, central refers to portions inside the edges, but an exactly central position is not implied.
By “pinch” what is meant herein is that a balloon surface is folded at a small area, creating a portion where the balloon is bilayered. In other words, the surface is bent and the two surfaces on either side of the bend brought together so as to be juxtaposed or directly adjacent. This pinch can be glued or otherwise welded, making the bilayer structure permanent. Outside of the pinch area, the balloon has the usual single layer structure.
By “fold inside” or “pinch inside” or “folded internally” or any similar phrases, what is mean is that the material is folded such that the outer surfaces of the balloon are in juxtaposition, and so that the bilayer portion is “inside” the balloon.
By “conforming depression” what is meant is that the depression is retained even on hyperinflation or squeezing or otherwise constraining the balloon. Thus, the balloon holds its shape, even in the compressed, slippery, mobile environment inside the rectum, and will tend to continue to cradle the prostate, as opposed to letting it slide off the balloon surface.
By “baffle” what is a meant is a small strip of material of length less than the expanded width between the two surfaces to which it is welded. The baffle is thus welded to one or more surfaces of the balloon and/or the lumen, and serves to control the depth of a conforming depression, longer baffles leading to shallower depressions, shorter baffles leading to deeper depressions. The pinch described above, serves the same function as the baffle, but is not a separate piece of material, but made directly from the balloon surface material.
By “groove” what is meant is a depression that is longer than its width. By “dimple” what is meant is a depression that is about as long as its width.
By “pocket” herein what is meant is a small channel or tunnel or tube to enclose (preferably on 3 sides) the one or more sensors provided with the balloon. For a rectal balloon the pocket is preferably on the surface of the balloon that cradles the prostate and preferably coincides with the groove or dimple or other conforming depression. The pocket can be on the inner surface, allowing the sensor to be threaded through the lumen and into the pocket, but this is not essential and the pocket also be on the outer surface. For a reusable sensor this may be a better location, allowing the user to easily slip the sensor into the pocket in use, and remove it for sterilization after use (if needed).
A “plastic-scintillator radiation sensor” generally comprises a plastic scintillator optically couple to a fiber optic cable operatively coupled to an adaptor or connector, wherein the entire sensor is encased in an opaque jacket or otherwise protected from ambient light. The remaining portions of the system, e.g. detector, display unit, processors and the like are generally sold separately from the sensor cable, and are well known in the art and not detailed herein. The remaining portions of the system, e.g. detector and display unit, processors and the like are generally sold separately from the sensor cable, and are well known in the art and not detailed herein.
A “electromagnetic motion sensor” as used herein generally refers a sensor having 2 or 3 coils therein, which produce an electrical current in a variable magnetic field in which the motion sensors are located. These are electrically coupled to an adaptor or connector and the entire cable is electrically insulted. The remaining portions of the system, e.g. EM field generator, amplifier units (if any), display unit, processors and the like are well known in the art and not detailed herein. In one embodiment the motion sensors used herein utilize electromagnetic fields to determine motion thereof. Electromagnetic navigation systems are generally based on the Biot Savart law, the principle that in the presence of a known magnetic field generator, the magnetic field vector in a given location can be measured in terms of magnitude, direction, length, and proximity of the current generating the field by a sensor. Generally the motion sensor includes a transmitter assembly and a sensor assembly. The transmitters are typically in the form of coils, and mutually orthogonal relative to each other. The sensor assembly may have one or more sensors and capable of monitoring the magnetic fields generated by the transmitter assembly. The individual sensors may be coils, flexgate transducers, magneto-resistive sensors, Hall effect sensors or any other devices capable of providing precision measurements of magnetic fields. In practice, a small electromagnetic field generator in the form of a small, block-like device creates a small, differential magnetic field into which a sensor coil may be placed. This small field is typically only 50×50×50 cm, but can be larger or smaller for different applications. The coils detect the rapidly changing magnetic field, and per Faraday's law of electromagnetic induction, elicit a weak electrical current. It is the processing of this current within the magnetic field that allow delineation of the sensor, and thus, balloon position, within the confined space.
As an alternative, the sensors described herein can be wireless, in which case the pocket can be sealed completely around the sensor, providing a waterproof environment. However, the currently preferred sensors are wired, and thus include a cable and adaptor for connection to separate detector units.
The use of the word “a” or “an” when used in conjunction with the term “comprising” in the claims or the specification means one or more than one, unless the context dictates otherwise.
The term “about” means the stated value plus or minus the margin of error of measurement or plus or minus 10% if no method of measurement is indicated.
The use of the term “or” in the claims is used to mean “and/or” unless explicitly indicated to refer to alternatives only or if the alternatives are mutually exclusive.
The terms “comprise”, “have”, and “include” (and their variants) are open-ended linking verbs and allow the addition of other elements when used in a claim. The phrase “consisting of” excludes additional elements, and the term “consisting essentially of” excludes material elements, but allows the inclusion of nonmaterial elements, such as labels, instructions for use, radio-opaque markers, stoppers, and the like.
Referring to
The shaft 12 is a generally longitudinal shaft and has a fluid passageway extending through the center thereof. The shaft 12 is made of a flexible material, and can bend slightly to conform to the rectum and provide comfort, but still be stiff enough to be inserted thereinto.
A valve assembly 22 is affixed to the shaft 12 opposite the balloon 14. The valve assembly 22 can have a variety of configurations.
The opposite end 16 of the shaft 12 contacts the end 32 of the balloon 14. The end 16 is preferably curved or dome-shaped so as facilitate the introduction of the balloon 14 into the rectum. The shaft 12 has numerical or other indicia 34 formed therealong. These numerical references are indicative of the distance that the balloon 14 has been inserted into the rectum. As such, the indicia 34 provide a clear indication to the medical personnel of the desired location of the rectal balloon 14. Here, the stopper is shown positioned at indicia 34 number “55.”
A ring 19 is affixed to the shaft 12 adjacent to the balloon 14. This ring 19 can be of a bright color, such as blue, so as to provide the medical personnel with positive indication of when the balloon 14 is past the anal verge. The ring 19 is approximately 5 millimeters long. The stopper 13 is shown as positioned away from the balloon 14. This would be the position prior to insertion. The stopper 13 is slidably mounted on the shaft 12. The stopper 13 has a semi-spherical shape so as to conform to the entrance of the rectum. A suitable locking mechanism can be provided so as to fix the stopper at a desired location.
After the procedure has been completed, the balloon 14 can be deflated and easily pulled outwardly of the rectum in its deflated condition. In
Importantly, in
The sensor 70 can be chosen from any of the available implantable sensors that enable user to monitor the radiation dosage for external beam radiation therapy devices. A particularly preferred sensor is the sensor described in 61/481,503, filed May 2, 2011, and the utility filing related thereto Ser. No. 13/444,584, filed Apr. 11, 2012, and expressly incorporated by reference herein in their entirety. That sensor is a plastic scintillator detector cable comprising a single, short length of scintillator fiber operably coupled to a suitable length of optic fiber, which has a standard data coupler or connector at the end of the cable opposite the scintillator fiber. The scintillator detector is thus at the distal end of the cable and a suitable data coupler is at the proximal end, and the entirety of the cable is enclosed in a flexible, opaque covering (e.g., the typical wire jacket).
In another embodiment, the cable has at least two separate, but closely juxtaposed, plastic scintillator detectors. The two detectors are parallel, but offset from one another in the longitudinal axis, so that radiation can be simultaneous assessed at two ends of a target, such as on either end of the prostrate or both ends of an irradiated throat area, and the like.
In preferred embodiments, this sensor cable is contained in the layer between the upper and middle layers of the balloon, thus being protected from the environment and immediately adjacent the prostate, and the distal end of the cable affixed to at least a portion of the shaft such that the connectors extend outside the body cavity and can be plugged into the appropriate device (e.g., a scintillation counter).
A further benefit can be realized by utilizing an additional fiducial marker in the form of a radioactive seed implanted or injected into the prostate. The radioactive seed combined with the fiducial markers 72 allows for triangulation to make certain that the balloon is in the correct position for treatment.
Additional benefit can be realized if the fiducial marker is contained on or within the cable. For example, the fiducial marker can be at the tip or on the surface of the cable, and in fact, the fiducial marker can be positioned inside the cap designed in Ser. No. 13/444,584. It could also be placed on or inside the tip of the balloon shaft.
A plurality of holes 48 are formed in the shaft 12 through which the balloon 14 is filled with fluid. The plurality of holes 48 are formed within the balloon 14 so as to allow fluid to be introduced into and removed from the balloon 14. It can be seem that each of the holes 48 is spaced from and offset by 90° from an adjacent hole around the diameter of shaft 12. A total of six holes are formed in the shaft 12 within balloon 14 so as to allow the fluid to pass from an interior of shaft 12 to the interior of the balloon 14. This arrangement of holes 48 facilitates complete extraction of the fluid from the balloon 14. Under certain circumstances, one of the holes may become clogged or blocked by contact between the body and the balloon, the staggered arrangement of holes assures that the unblocked holes 48 allow the fluid to continue to be easily extracted.
In
As discussed above, the groove 52 at the central seating area 46 engages with the tip of the prostate to reduce the lateral movement of the balloon. To achieve that, however, it is important that the groove 52 maintains its shape even when the balloon 14 is subject to external pressure when put inside a patient's rectum. The groove 52 is thus formed by welding or otherwise attaching the top layer 78 with the middle layer 80 at the groove bottom 71. This way, a recessed area 52 with some depth can be maintained, thus its engagement with the patient's prostate, regardless of the external pressure that may or may not cause the remainder of the balloon to deform. A skilled artisan can understand that the bonding between the top layer 78 and the middle layer 80 at the groove bottom 71 can be achieved by other equivalent methods known in the field.
In general, the present invention assures uniformity and reproducibility of positioning. The stopper 13 provides an initial indication of the depth of positioning of the balloon 14. It is possible that the balloon 14 could have an improper rotational position in the rectum. A proper orientation of the balloon 14 is achieved by viewing the fiducial markers 72 by any imaging system. The lateral flatness of the balloon 14 is assuredly positioned against the prostate. In essence, the prostate is wedged by the inflated balloon into the dimple created by the groove 52, and is unable to slip from one side to the other as in the prior art non-conforming balloons. The sensor 70 is thereby properly positioned at the same location during all treatments. The sensor 70 can then be used to accurately determine the amount of radiation delivered during each external beam radiation treatment.
In use, the sensor cable is outfitted with adaptors for connection to the requisite radiation detector instrumentation, such as CCD camera, photodetector, photomultiplier tube, scintillation counter, MOSFET, vacuum photodetector, microchannel plates, and the like, which operably connects with a processor having the needed software to assess and report radiation dose.
Using the rectal balloon with fiducial markers and radiation sensor described herein, the radiologist can accurately position the balloon, wedge the prostate into the groove by inflation, and determine exactly where the device is using a variety of imaging means. Further, the radiologist can accurately measure radiation dose at multiple locations on the prostate, thus allowing further refinements in dosimetry.
This balloon has a top layer 104, a middle layer 105, and a bottom layer 106, which are welded together along the outer edges (not shown), and also affixed to the lumen, in this case at both the distal and proximal ends. The top layer 104 is welded 107 to the middle layer 105 along the central line of the balloon, but shifted proximately, so that the distal portion of the balloon bulges 108 more than the proximal portion on hyperinflation. The middle layer also has holes or gaps 109 so that the balloon comprises only a single fluid chamber and thus needed only a single fill means, but dual fluid filling means could be provided for a two chamber balloon (see e.g., US20130123621). The balloon filling means (typically a lumen, stock cock and luer connector) are not labeled in this figure, but are typical in the art.
The weld 107 of top layer 104 to middle layer 105 provides a groove 1010 (or indent or depression) having some depth into which the prostate can be wedged, and this grooved depression is retained on inflation, and even on hyperinflation, or in the constrained environment of the rectum. Although a groove 1010 is shown, a dimple could also suffice, and the weld could be made shorter. The physical coupling of the middle baffle layer to the top layer provides a physical restraint against expansion or stretching, and the balloon is conforming—that is it holds its shape even in the highly mobile constrained environment of the rectum.
We now show how to make a similar conforming shaped balloon using a unitary or binary balloon construction and fewer welds.
A unitary balloon is made by any conventional method and in any desired shape. For example, a tubular form is heated, immersed in a tank of coagulant solution for a few seconds, heated again and then immersed in a tank of latex. The coagulant causes the latex to coat the form, and the longer the forms are left in the tank, the thicker the coating that sticks to them. The forms must be inserted and removed at carefully controlled speeds to avoid trapping air bubbles and to achieve an even, thin coating. The coated forms are then immersed in a tank of leaching solution (often plain water) to dissolve and leach away excess coagulant, and the rubber or polymer on the forms is dried and cured as needed. The balloons are then mechanically removed from the forms, e.g., with a spray of water or air.
Whether the balloon is unitary or binary (two layers), the balloon can then be shaped to make a conforming depression, as shown in
The lumen 1129 is also coated with a spot of glue and inserted into the balloon, such that the pinch 1121 is then welded 1123 to the lumen. This can also be done with jigs to hold the balloon and lumen. The balloon is welded to at least the distal end of the lumen, preferably both ends, valve means are provided and if needed the balloon is sterilized before packaging. The position of the lumen and depth of groove can be influenced by changing the amount or depth of balloon pinch (-d-), a smaller pinch weld moving the lumen closer to the edge of the balloon and making the groove more shallow.
Although we describe a unitary balloon, it is also possible to make the shaped balloon in two layers. See e.g., optional edge weld 1137. In some cases the two-layer construction may make the pinch/lumen welds easier, especially where the balloon is quite small and it is difficult to create a weld inside a unitary balloon. The balloon is as described above, but an additional weld 1137 is shown at the outer edges of the two layers 1133 and 1135. The use of two layers also means that the two layers can be made of different materials, e.g., a less stretchy or thicker material on one side that will not stretch as much and thus provide a flatter surface. When the device is welded, it can be inverted so as to put the edge welds, which can be stiff or sharp, on the inside of the balloon if needed.
A rectal balloon 1257 is shown in cross section along its longitudinal axis in
The pinch weld is shown at 1255, and the weld to the lumen 1253 is shown in black. Additional welds 1263 and 1265 are to the distal and proximal ends of gas lumen 1259. The depression or groove 1251 is thus clearly seen. On hyperinflation, the distal end of balloon 1257 will bulge distally of the groove 1251 (not shown) since there is more material here, and thus, there will be more stretch.
In yet another variation, the pinch can be replaced with a baffle that is a small piece or strip of film welded at both the top layer and the lumen, wherein the width of the baffle controls the depth of the groove.
Using the pinch weld, lumen welds and layer to layer welds as described herein, it is possible to make a shaped balloon with one or more conforming depressions anywhere on its surface. Further, bulges can be created with thinner or more elastic material, or shaped on a unitary balloon mold, or cut in a two layer balloon outline, as desired. Thus, using the principles described herein, a variety of conforming shapes are possible.
In
The pocket need not be made using a fourth layer, but instead the sensor can fit into the weld between the top and middle or lumen layer if that weld is U-shaped, thus leaving an opening, pocket or tunnel into which the sensor can be threaded.
Alternatively, a pocket can be provided on the outer surface of a rectal balloon, and the pocket can lie within the dimple or groove, or a pair of pockets could pass on either side if desired.
In
The radiation sensor cable 1101 also has a detecting end 1105, and the diameter of the cable should be smaller than that of the port 1009 and the tunnel 1017. When installing, the detecting end 1105 of the radiation sensor 1101 is inserted in the port 1009 into the tunnel 1017, and eventually reached the seating area 1015. The radiation sensor 1101 can further be locked in place by the hub 1011 for consistent placement. The radiation sensor cable 1101 is preferably made of flexible material due to the irregular shape of the balloon and the design of the tunnel 1017.
In more detail the detector end 1105 of the radiation sensor 1101 is shown in
The proximal end of the cable is outfitted with a standard coupler, in this case an SCRJ coupler, for reversible connection to a separate detector unit that detects and quantifies the signal obtained by the plastic scintillator fiber and transmitted via optic fiber to the detector unit. Any of the known detectors can be used, including a light sensor such as a photomultiplier tube (PMT), photodiode, PIN diode or CCD-based photodetector. Such device is typically connected to or outfitted with a processor and display for displaying radiation dosage to the medical practitioner.
Motion sensors are commercially available in the art. For example, Northern Digital Inc. offers the Aurora Electromagnetic Measurement System having miniaturized sensors designed specifically for medical uses. Advantageously, no line of sight is required for this device because it does not rely on optical signals. The Aurora system (e.g., U.S. Pat. No. 5,923,417, U.S. Pat. No. 6,061,644, US20120226094, each of which is incorporated herein by reference in its entirety) includes a Field Generator (FG) that emits a low-intensity, varying electromagnetic field and establishes the position of the tracking volume. Small currents are induced in the sensors by the varying electromagnetic fields produced by the Field Generator. The characteristics of these electrical signals are dependent on the distance and angle between a sensor and the Field Generator. A Sensor Interface Units (SIU) amplifies and digitizes the electrical signals from the sensors and provides an increased distance between the System Control Unit and sensors, while minimizing the potential for data noise. The System Control Unit collects information from the SIUs, calculates the position and orientation of each sensor and interfaces with the host computer. Software is provided therewith that can be customized for the users specific applications.
In more detail, the patient is first placed within electromagnetic fields, preferably generated by the Field Generator located between the patient and the bed for treatment. The system determines the location of objects that are embedded with sensor coils. When the object (in this case a balloon having the sensor coil inside a patient) is placed inside controlled, varying magnetic fields, voltages are induced in the sensor coils. These induced voltages are used by the measurement system to calculate the position and orientation of the object, as well as being compared with prior values. As the magnetic fields are of low field strength and can safely pass through human tissue, location measurement of an object is possible without the line-of-sight constraints of an optical spatial measurement system.
One preferred sensor is the Aurora sensor 610020, which is built to order and is 2.3 mm diameter×4 mm length and can be sterilized via autoclave and is known to survive more than 20 autoclave cycles. Another preferred sensor is the Aurora sensor 610029, which is 0.8 mm diameter×9 mm length and is particularly suitable for disposable applications. Other Aurora sensors of various size and bending radius can also be used, as long as they fit within the pocket designed for the motion sensor,
In one embodiment, the motion sensor continuously monitors the location of the balloon, which serves as a surrogate method for assessing intrafraction prostate motion. The balloon allows the user (medical practitioner) to view the tip of the medical instrument, for example a flexible endoscope or in this case endorectal balloon. In this embodiment, a 6DOF sensor is provided at the tip of the apparatus, with six additional sensors distributed along the distal length. By combining this electromagnetic motion sensor with the rectal balloon apparatus, it is possible to calculate and render the apparatus' shape in real time, as well as tracking the movement of the anterior rectal wall at the rectal-prostate interface. This significantly increases the accuracy of treatment and reduces potentially serious side effect.
Further, this combination apparatus of motion sensor and rectal balloon is based on (x, y, z) navigation technology designed specifically for medical application. Based on electromagnetic technology with no line-of-sight requirements, the apparatus tracks the miniaturized sensors designed for integration into the rectal balloon device. The depth of the balloon is customized during the imaging procedure so the location of the sensor will set in a fixed location adjacent to the rectal prostatic interface.
The placement and spacing of the sensors can be customized for specific applications. In addition, the tool can be sterilized and reused, providing more economical advantages for the balloon apparatus.
The foregoing disclosure and description of the invention is illustrative and explanatory thereof Various changes in the details of the illustrated construction can be made within the scope of the present claims without departing from the true spirit of the invention. The present invention should only be limited by the following claims and their legal equivalents.
The following citations are incorporated by reference herein in their entireties for all purposes:
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The present application is a continuation-in-part (CIP) of U.S. Ser. No. 13/444,626, filed on Apr. 11, 2012, allowed, which is a CIP of U.S. Ser. No. 12/141,270, filed on Jun. 18, 2008, abandoned, which is a CIP of U.S. Ser. No. 12/034,470, filed on Feb. 20, 2008, now patented as U.S. Pat. No. 8,080,031, which is CIP of U.S. Ser. No. 11/933,018, filed on Oct. 31, 2007, abandoned, which is a CIP of U.S. Ser. No. 11/623,702, filed on Jan. 16, 2007, abandoned, and all of which are incorporated by reference herein in their entirety for all purposes. The present application is also a CIP of Ser. No. 13/299,348, filed Nov. 17, 2011, pending, which is a CIP of U.S. application Ser. No. 12/707,389, filed Feb. 17, 2010, now issued as U.S. Pat. No. 8,500,771, which is a CIP of U.S. application Ser. No. 12/412,017, filed Mar. 26, 2009, abandoned, which is a CIP of U.S. application Ser. No. 12/410,639 filed on Mar. 25, 2009, now issued as U.S. Pat. No. 8,454,648 on Jun. 4, 2013, which is a CIP of U.S. application Ser. No. 12/141,270 filed on Jun. 18, 2008, abandoned, which is a CIP of U.S. application Ser. No. 12/034,470, filed Feb. 20, 2008, now issued as U.S. Pat. No. 8,080,031, which is a CIP of U.S. application Ser. No. 11/966,544 filed on Dec. 28, 2007, abandoned, which is CIP of U.S. Ser. No. 11/933,018, filed on Oct. 31, 2007, abandoned, which is a CIP of U.S. Ser. No. 11/623,702, filed on Jan. 16, 2007, abandoned, and all of which are incorporated by reference herein in their entirety for all purposes. The is invention is a CIP of Ser. No. 13/591,546, filed Aug. 22, 2012, pending, which is also incorporated by reference herein in its entirety.
| Number | Date | Country | |
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| Parent | 13444626 | Apr 2012 | US |
| Child | 14065127 | US | |
| Parent | 12141270 | Jun 2008 | US |
| Child | 13444626 | US | |
| Parent | 12034470 | Feb 2008 | US |
| Child | 12141270 | US | |
| Parent | 11966544 | Dec 2007 | US |
| Child | 12034470 | US | |
| Parent | 11933018 | Oct 2007 | US |
| Child | 11966544 | US | |
| Parent | 11623702 | Jan 2007 | US |
| Child | 11933018 | US | |
| Parent | 13299348 | Nov 2011 | US |
| Child | 11623702 | US | |
| Parent | 13591546 | Aug 2012 | US |
| Child | 13299348 | US |
