CA1287449C - Unitary inflatable penile prosthesis - Google Patents
Unitary inflatable penile prosthesisInfo
- Publication number
- CA1287449C CA1287449C CA000502420A CA502420A CA1287449C CA 1287449 C CA1287449 C CA 1287449C CA 000502420 A CA000502420 A CA 000502420A CA 502420 A CA502420 A CA 502420A CA 1287449 C CA1287449 C CA 1287449C
- Authority
- CA
- Canada
- Prior art keywords
- fluid
- reservoir
- tubular portion
- prosthesis
- tubular
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/26—Penis implants
Abstract
A UNITARY INFLATABLE PENILE PROSTHESIS
ABSTRACT
A unitary, inflatable penile prosthesis system includes a prosthesis implantable within the corpus cavernosum of the penis in order to alleviate erectile impotency. A tubular enclosure includes a distal pump, a medial pressurizable chamber, and a proximal fluid reser-voir. A pump draws fluid from the reservoir through an external fluid passageway into the pressurizable chamber.
The pressurizable chamber is defined by an internal, tubular, substantially nondistensible portion and a concentric tubular sleeve. The nondistensible portion is crimped so that it may expand in diameter. Upon expansion, the prosthesis assumes a straight, erect state.
The sleeve may elastically bias the nondistensible portion to its flaccid state. Fluid for filling the nondistensible portion may be stored in a rear fluid reservoir having a rigid internal stabilizer.
ABSTRACT
A unitary, inflatable penile prosthesis system includes a prosthesis implantable within the corpus cavernosum of the penis in order to alleviate erectile impotency. A tubular enclosure includes a distal pump, a medial pressurizable chamber, and a proximal fluid reser-voir. A pump draws fluid from the reservoir through an external fluid passageway into the pressurizable chamber.
The pressurizable chamber is defined by an internal, tubular, substantially nondistensible portion and a concentric tubular sleeve. The nondistensible portion is crimped so that it may expand in diameter. Upon expansion, the prosthesis assumes a straight, erect state.
The sleeve may elastically bias the nondistensible portion to its flaccid state. Fluid for filling the nondistensible portion may be stored in a rear fluid reservoir having a rigid internal stabilizer.
Description
~.287449 4~80-364 P.C. 7001 A ~JNITARY I~FJ~ATA~T.J~ PENIL~ PROST~ESIS
This invention relates generally to methods and devices for alleviating erectile impotency, and specifically to unitary, inflatable devices which may be implanted within the corpus cavernosum cf the penis.
A number of devices are commercially available for enabling those with erectile impotency to achieve an erection. These devices are ~enerally implanted within the corpus cavernosum of the penis. Normally two such devices are utilized, one implanted into each corpus cavernosum. Modern day technology has evolved from the early rigid rod devices that produced a permanent erec-tion. Since the user had no ability to control the operation of the device, the rigid rod approach had serious drawbacks.
The so-called inflatable penile prostheses generally include a reservoir, a pump, and a pressure chamber.
Fluid is pumped from the reservoir by the pump to the pressure chamber in order to achieve an erection. Early devices such as that disclosed in U. S. Patent 3,853,122 to Strauch, et al., used an external pump and a simple tube and valve mechanism. U. S. Patent 3,954,102 to Buuck discloses an improvement wherein the device may be manually operated in a convenient fashion through the use of a bypass valve means.
U. S. Patent 4,009,711 discloses a penile prosthesis with an external pump and a non-distensible tail that is 328~
implanted at the root of each corpus cavernosum under the puboischiatic rami. The patent indicates that the tail-like portion provides increased stability when the penis becomes erect and decreases considerably the volume of fluid needed for an adequate erection.
A penile prosthesis using an inflatable hinge is described in U. S. Patent ~,267,~29 to Burton and Mikulich. In this patent, a tubular section includes a chamber which undergoes only a small chan~e in volume and therefore requires minimum fluid displacement as the prosthesis transforms from a non-erect to an erect condi-tion. Unitary penile prostheses which include a pair o~
concentric chambers, one of which is pressurized, are disclosed in U. S. Patents 4,353,360 and 4,399,811. In these patents, the inner of two concentric chambers is pressurized while the outer of the two chambers acts as the fluid reservoir prior to erection. To attain an erection, fluid is pumped from the outer reservoir throu~h a pump to the inner reservoir. Thus, the total volume of the two chambers is always constant.
The present invention provides a dependable, unitary, inflatable penile prosthesis with a low fluid volume that is convertable from a non-erect to an erect state without re~uirin~ a substantial volume chan~e. The volume of the portion of the device that includes the pressurizable chamber increases when transformed to the erect state.
The medial portion of the prosthesis may be smaller in the flaccid state and may deflate readily and naturally.
Moreover, a fluid reservoir external of the pressurizable chamber is provided that may add a fluid volume safety factor.
In accordance with the present invention, a unitary penile prosthesis implantable within at least one corpus cavernosum of the penis includes an implantable, broadly tubular enclosure. A generally tubular pressurizable chamber section is defined medially within the enclosure. The chamber section includes a substantially nondistensible tubular portion and a tubular sleeve concentric with the tubular portion. The tubular portion is expandable from a flaccid to an erect state when the interior volume of the tubular portion is substantially filled to capacity. A fluid containing reservoir is defined withln the enclosure in series along the len~th of the enclosure with respect to the chamber section. A manually compressible pump is defined within the enclosure in series along the len~th of the enclosure with respect to the chamber section. The pump is adapted for fluid communication with the tubular portion. A passa~eway ~luidically connects the reservoir and the pump while being maintained in fluid isolation from the chamber section. The pump is adapted to pump fluid to the tubular portion from the reservoir such that the volume of the chamber section increases as the chamber section is transformed from its flaccid to its erect state. The reservoir and the pump are located on opposite sides of the chamber section.
,. . . .
~L28744~3 In accordance with one preferred embodiment of the present invention, the reservoir is capable of holding a substantial portion of the fluid needed to transform the tubular portion from its flaccid to its erect state.
In accordance with yet another preferred embodiment of the present invention, the chamber section includes a substantially nondistensible tubular portion and a tubulax sleeve concentric with and surrounding the tubular portion. The reservoir is adapted to be proximally situated with respect to the chamber section and includes a rigid internal stabilizing member. The reservoir is capable of holding a substantial portion of the fluid needed to transform the tubular portion from its flaccid to its erect state, such that the volume within the sleeve in the erect state is greater than the volume within the sleeve in the flaccid state.
-- ~Z87449 In accordance with another preferred embodiment of the present invention, the implantable, broadly tubular enclosure has a front tip that is substantially rigid in the erect state. The reservoir is adapted to hold a substantial portion of the fluid needed to transform the tubular portion from its flaccid to its erect state such that the volume of the chamber section increases as the chamber section is transformed from its flaccid to its erect state.
Figure 1 is a side elevational vie~ of one embodiment of the present invention, in use, in its flaccid state;
Figure 2 is a side elevation view of the embodi~nent shown in Figure 1 in its erect state;
- :~287~49 Figure 3 is an enlarged vertical cross-sectional view taken generally along the curve 3-3 in Figure 1;
Figure 4 is a cross-sectional view taken generally along the line 4-4 in Figure 1 of one embodiment in the flaccid state;
Figure 5 is a cross-sectional view taken generally along the line 5-5 in Figure 2 of one embodiment in the ereet state; and ` ~Z87449 Figure 6 is an enlarged cross-sectional view of the valving portion of the prosthesis shown in Figure 3.
Referring to the drawing wherein like reference characters are utilized for like parts throughout the several views, a unitary, inflatable penile prosthesis 10, shown in Figure l, includes an implantable, broadly tubular enclosure 12 sized to be implanted within one corpus cavernosum of the penis. Normally two devices of the kind shown in Figure l are implanted, one in each corpus cavernosum. However, the present invention is adaptable for use with double cylinder designs in which one prosthesis is used to fill both corpus cavernosa. The outer layer of the tubular enclosure 12 is advanta~eously made up of material which is biocompatible. One particularly suitable material for this purpose is silicone, since it is readily accepted by the human body when used with indwelling devices.
The enclosure 12 includes a proximal section 14, a pressurizable medial section 16, and a distal portion 18.
2S Normally the proximal section 14 is positioned in the rear of the corpus cavernosum under the puboischiatic rami. As shown in Figure 3, the proximal section 14 defines a rear fluid reservoir 20. A rigid stabilizer 22 extends rearwardly from the medial section 16 centralLy through the fluid reservoir 20 to a rounded end 26 in contact with the rear tip 24. The stabilizer 22 serves to maintain the shape of the rear fluid reservoir 20 and provide rigidity regardless of the amount of fluid contained therein.
Conveniently the rear tip 24 has a slightly tapered external configuration as a result. A conventional rear --` 1287449 tip extender (not shown) may be provided to lengthen the enclosure 12, if necessary.
The distal section 18 advantageously includes a front tip 25 that is substantially rigid, so as to resist bucXling during intercourse, at least in the erect state.
Advantageously the tip 25 is rigid in both the erect and flaccid states. If desired, the front tip may be made substantially solid.
The medial section 16 defines a pressurizable chamber 28. The medial section 16 is positioned along the length of the enclosure 12 such that it tends to lie medially along the length of the corpus cavernosum and particularly so that it lies substantially in the portion of the corpus cavernosum which is distal of the body plane. Thus, the pressurizable chamber 28 may provide an inflatable hinge, as will be described in greater detail hereinafter~
As shown in Figure 4, the pressuri7able chamber 28 is defined by a tubular portion 30 which is concentrically contained within a tubular sleeve 32. The tubular portion 30 may be formed of two layers includin~ an inner layer or bladder 34 and a substantially non-distensible layer 36.
The non-distensible layer 36 may take a variety of forms, but advantageously it is formed from a tubular section of woven dacron material, such as a prosthetic vascular graft. The inner layer 34 may be formed of a substantially liquid impervious material, such as silicone.
Adjacent proximal ends of the tubular portion 30 and tubular sleeve 32 are anchored to the plug 40 which also secures the distal end of the stabilizer 22, as shown in 12~37449 .
_9_ Fi~ure 3. The plug 40 fills the internal volume of the enclosure 12 with the exception of an axial passageway 42.
On the distal end of the pressurizable chamber 28, the tubular portion 30 and sleeve 32 are anchored to the valve plug 46. Like the plug 40, the valve plug 46 fills a portion of the interior of the enclosure 12. In this way, the intermediate portion of the tubula-r sleeve 32 and portion 30 extend between the plugs 40 and 46 in an unsupported fashion. Thus, when the prosthesis 10 is in a flaccid state, as shown in Eigure 1, the portion 30 and sleeve 32 may tend to neck or sag inwardly.
As shown in Figure 4, the tubular portion 30, in its flaccid state, includes a crimp or fold 48. The crimp 48 provides for extra expansion of the tubular portion 30 in order to completely fill the tubular sleeve 32 in its expanded configuration. Because of the nature of the material of the portion 30, it ~enerally expands in girth to a full tubular configuration, as shown in Figure 5, and then comes to a complete stop after which no further expansion or distension is possible. ~hus the change in volume between the position shown in Figure 4 and the position shown in Figure S wherein the portion 30 is essentially unfolded, is relatively small.
The tubular sleeve 32 may be distensible or non-distensible. In one preferred embodiment it is made of a distensible, stretchable, elastic material such as silicone. With an elastic sleeve 32 the relaxed volume of the sleeve 32 may correspond closely to the flaccid volume of the portion 30 so that the sleeve 32 always conforms closely to the configuration of the portion 30. Moreover, with an elastic sleeve 32, the sleeve 32 elastically ~l28~ 9 resists the expansion of the tubular portion 30 from its flaccid to its erect state.
The valve plug 46, shown in Figure 6, includes a bypass valve 50, an inlet valve 52, and an exit valve 54.
The inlet valve 52 communicates on one end with a manually compressible pump 55 defined within the distal portion 18 of the enclosure 12. The inlet valve 5~ communicates on its proximal end with a radially oriented passageway 58.
The radially oriented passageway 58 communicates with a transverse, radially oriented passageway section 60. The passageway 58 and the section 60 communicate with an axial, lengthwise passageway 62 by way of the annular chamber 63 defined by the sleeve 32~ The passageway 62 extends from the distal portion 18 to the proximal portion 14 in fluid isolation from the pressurizable chamber 28.
It empties into the axial passageway 42 and ultimately into the rear fluid reservoir 20.
Regardless of the state of the portion 30 and sleeve 32, communication through the passageway 62 is always possible. The passageway 62 also communicates with the region 64 between the portion 30 and sleeve 32, but only at the point 66 adjacent the axial passageway 42 and at 25 the point 103 adjacent the axial passageway 63. Thus the fluid within the region 64 may be exhausted rearwardly through the prosthesis 10 into the slot 68 defined in the plug 40 and stabilizer 22.
The outlet valve 54, sho~n in Eigure 6, communicates with the manually compressible pump 56 on the distal end and communicates on the other end with the region surrounding the bypass valve 50. Specifically a continuously open passageway 70 is provided across the bypass valve 50 to the interior of the tubular portion 30.
~`2~3~449 Each of the valves 52 and 54 includes an enlarged housing 72, a coiled spring 74 and a valve member 76. The coiled spring 74 biases the valve member 76A of the valve 54 distally while the coiled spring 74 of the valve 52 biases its valve member 76B proximally. The sealing face 78 of each valve 52, 54 seals on an adjacent transversely oriented ledge 80. The sealing faces 78 of the valves 52 and 54 are concave which encourages formation of a good seal. The valves 52, 54 each include a necked down region 82 in the housing 72 proximate to the ledge 80.
The bypass valve 50 includes a generally conical housing 84 with a proximally extending port 86 and a distally extending seat 88. The seat 88 is generally conical as well and communicates with the passageway 90 that in turn communicates with the passageway 58. A ball 92 is normally seated on the seat 88 closing the passageway 90. One or more extensions 94 defined on the conical housing 84 aligned with the passageway 96 permit generally continuous fluid communication from the passageway 96 to the interior of the tubular portion 30.
~owever, reverse flow into the passageway 90 is normally prevented by the ball 92.
A fillin~ port 44 may enable fluid communication between the exterior of the enclosure 12 and the rear fluid reservoir 20 for fluid insertion. A hypodermic needle may be inserted into the port 44 through a central aperture 47 in the base 49 of the stabilizer 22. When the end of the needle reaches the slot 68, the fluid then flows into the reservoir 20. After the needle is re-tracted the port 44 is filled with a sealant 45.
The prosthesis 10 may be operated in the following fashion. Initially a sufficient amount of fluid, such as ~28'7449 a physiological solution, is loaded into the rear fluid reservoir 20 and tubular portion 30. The fluid may be inletted to the fluid reservoir 20 initially and then pumped to the portion 30 as will be described hereinafter.
In any case, the portion 30 contains sufficient fluid to assume the configuration shown in Figure 4. In the flaccid state the portion may contain at least about 50%
of its capacity and in one illustrative embodiment it contains about 90% of its capacity.
The rear fluid reservoir 20 is filled with at least a substantial portion of fluid needed to permit pumping o the fluid from the reservoir 20 through the pump 56 to fill the added tubular portion 30 volume required to transform from the flaccid state shown in Figures 1 and 4 to the erect, filled to capacity state shown in Figures 2 and 5 wherèin the tubular portion 30 is taut and pressurized. For example, the reservoir 20 may contain from about 20% to 100~ of the fluid needed to transform the portion 30 to its erect state. Advantageously, the reservoir 20 contains from about 50% to about 70% of the fluid needed to transform the chamber 28 from the flaccid to the erect state. Additional fluid volume to pressurize the tubular portion 30 may be stored, for example, in the space 64 between the sleeve 32 and portion 30. Normally it will be necessary for the rear reservoir 20 and other fluid storage volumes to contain slightly more ~luid than that which would be held in the difference in the tubular portion 30 vol-tmes shown in Figures 4 and 5, because it is ~0 necessary to prime the various pumping passageways in order to get sufficient 1uid to the tubular portion 30.
Also, it is desirable to provide additional fluid capacity as a safety factor to insure that an erection can be maintained under all normal circumstances. In any case, the necessary fluid amounts can be easily determined in ~287~a~9 practice by those skilled in the art, and depend on the sizes of the various components utilized.
The prosthesis lO is then implanted within the corpus cavernosum of the patient. This may be done using con-ventional surgical techniques well known in the implanta-tion of inflatable penile prostheses. The proximal section 14 is positioned in the rear region of the corpus cavernosum and the distal section 18 in the distal region of the corpus cavernosum. It may be necessary in certain circumstances to use rear tip extenders for the proximal end in a fashion well known in the art to achieve a correct fit.
In order to operate the implanted prosthesis 20, the user initially compresses the manually compressible pump 56 externally of the penis. The compression of the flexible manually compressible pump 56 forces any fluid contained within the pump 56 into the pressurizable chamber 28~ This is because the pressure increase within the pump 56 forces the valve 54 open allowin~ fluid to flow around the valve member 76A through the passageway 70 past the ball 92 and around an extension 94. The user may continue to successively depress the pump 56 until the pressure within the pressurizable chamber 28 becomes sufficiently great that the valve member 76A no longer unseats from the sealin~ surface 78. At the same time, the compression of the pump 56 seals the inlet valve 52 closed.
Each time the user releases the pump 56, its walls spring back to their original position. This creates suction within the pump 56, opening the valve 52 and drawing fluid into the pump 56. The fluid is drawn from -the reservoir 20 through the passageway 62. When the suction subsides, the valve 52 springs closed.
In the erect or substantially rigid configuration, 5 the tubular portion 30 and sleeve 32 are puffed outwardly slightly from the configuration shown in Figures 1, 3, and 4, to that illustrated in Figures 2 and 5. Moreover, the prosthesis 10 is straight rather than angled or L-shaped.
The sleeve 32 is stretched radially outwardly so as to fit 10 snugly about the tubular portion 30.
In the flaccid state, the prosthesis 10 bends to accommodate to the natural flaccid shape of the penis.
The bending occurs along the pressurizable chamber ~8 15 which essentially acts as a hinge.
To resume the flaccid state after an erection, the valve plug 46 is squeezed externally. As a result of the deformation of the conical housing 84 and seat 88, 1uid 20 is allowed to flow from the pressurizable chamber 28 past the ball ~2 and into the passageway 90. From there the fluid may flow through the passage 60 or the passage 58 to the passageway 62. ~3ecause of the pent up pressure within thè pressurizable chamber 28, the fluid is forced 25 rearwardly through the passageway 62 into the rear fluid reservoir 20 where it is stored for use in the next erection. When the pressure within the chamber 28 has subsided sufficiently, manual actuation of the bypass valve S0 no longer has any effect on fluid outflow from 30 the pressurizable chamber 28 and the prosthesis 10 is in equilibrium. In this state the prosthesis 10 assumes a substantially flaccid configuration and bends with the penis so as to fold along the pressurizable chamber 28.
~l2874~9 ~ ith the present invention the volume of the pressurizable chamber 28 is nonconstant during expansion to erection. This is because at least a portion of the fluid required to achieve the erect state is obtained from sources external of the chamber 28, for example from the rear reservoir 20. Thus, the volume of the chamber 28 increases as the chamber 28 transforms to its erect state.
A fluid volume safety factor may be provided, with the present invention, without increasing the necessary girth of the flaccid prosthesis. This is because additional available volume may be provided without enlarging the medial portion 16 of the flaccid prosthesis.
With the present invention, the pressurizable chamber 28 and thus the prosthesis as a whole may be smaller in the flaccid state. The use of the rear reservoir 20 causes the device to take on a smaller flaccid configuration and to bend easily alon~ the medial portion 16. In addition, the prosthesis may deflate more readily and naturally. This is because the tubular sleeve 32 forces the portion 30 to assume its deflated configuration by pressing the fluid outwardly of the pressurizable chamber 28.
Because the integrity of the fluid passageway 62 remains inviolate and uncrimped, the egress of fluid from the pressurizable chamber 28 is assured and may be carried on in a relatively smooth fashion. Also, because the distension of the portion 30 is minimized, the tendency for faults or creases to block operation of the prosthesis lQ is lessened.
This invention relates generally to methods and devices for alleviating erectile impotency, and specifically to unitary, inflatable devices which may be implanted within the corpus cavernosum cf the penis.
A number of devices are commercially available for enabling those with erectile impotency to achieve an erection. These devices are ~enerally implanted within the corpus cavernosum of the penis. Normally two such devices are utilized, one implanted into each corpus cavernosum. Modern day technology has evolved from the early rigid rod devices that produced a permanent erec-tion. Since the user had no ability to control the operation of the device, the rigid rod approach had serious drawbacks.
The so-called inflatable penile prostheses generally include a reservoir, a pump, and a pressure chamber.
Fluid is pumped from the reservoir by the pump to the pressure chamber in order to achieve an erection. Early devices such as that disclosed in U. S. Patent 3,853,122 to Strauch, et al., used an external pump and a simple tube and valve mechanism. U. S. Patent 3,954,102 to Buuck discloses an improvement wherein the device may be manually operated in a convenient fashion through the use of a bypass valve means.
U. S. Patent 4,009,711 discloses a penile prosthesis with an external pump and a non-distensible tail that is 328~
implanted at the root of each corpus cavernosum under the puboischiatic rami. The patent indicates that the tail-like portion provides increased stability when the penis becomes erect and decreases considerably the volume of fluid needed for an adequate erection.
A penile prosthesis using an inflatable hinge is described in U. S. Patent ~,267,~29 to Burton and Mikulich. In this patent, a tubular section includes a chamber which undergoes only a small chan~e in volume and therefore requires minimum fluid displacement as the prosthesis transforms from a non-erect to an erect condi-tion. Unitary penile prostheses which include a pair o~
concentric chambers, one of which is pressurized, are disclosed in U. S. Patents 4,353,360 and 4,399,811. In these patents, the inner of two concentric chambers is pressurized while the outer of the two chambers acts as the fluid reservoir prior to erection. To attain an erection, fluid is pumped from the outer reservoir throu~h a pump to the inner reservoir. Thus, the total volume of the two chambers is always constant.
The present invention provides a dependable, unitary, inflatable penile prosthesis with a low fluid volume that is convertable from a non-erect to an erect state without re~uirin~ a substantial volume chan~e. The volume of the portion of the device that includes the pressurizable chamber increases when transformed to the erect state.
The medial portion of the prosthesis may be smaller in the flaccid state and may deflate readily and naturally.
Moreover, a fluid reservoir external of the pressurizable chamber is provided that may add a fluid volume safety factor.
In accordance with the present invention, a unitary penile prosthesis implantable within at least one corpus cavernosum of the penis includes an implantable, broadly tubular enclosure. A generally tubular pressurizable chamber section is defined medially within the enclosure. The chamber section includes a substantially nondistensible tubular portion and a tubular sleeve concentric with the tubular portion. The tubular portion is expandable from a flaccid to an erect state when the interior volume of the tubular portion is substantially filled to capacity. A fluid containing reservoir is defined withln the enclosure in series along the len~th of the enclosure with respect to the chamber section. A manually compressible pump is defined within the enclosure in series along the len~th of the enclosure with respect to the chamber section. The pump is adapted for fluid communication with the tubular portion. A passa~eway ~luidically connects the reservoir and the pump while being maintained in fluid isolation from the chamber section. The pump is adapted to pump fluid to the tubular portion from the reservoir such that the volume of the chamber section increases as the chamber section is transformed from its flaccid to its erect state. The reservoir and the pump are located on opposite sides of the chamber section.
,. . . .
~L28744~3 In accordance with one preferred embodiment of the present invention, the reservoir is capable of holding a substantial portion of the fluid needed to transform the tubular portion from its flaccid to its erect state.
In accordance with yet another preferred embodiment of the present invention, the chamber section includes a substantially nondistensible tubular portion and a tubulax sleeve concentric with and surrounding the tubular portion. The reservoir is adapted to be proximally situated with respect to the chamber section and includes a rigid internal stabilizing member. The reservoir is capable of holding a substantial portion of the fluid needed to transform the tubular portion from its flaccid to its erect state, such that the volume within the sleeve in the erect state is greater than the volume within the sleeve in the flaccid state.
-- ~Z87449 In accordance with another preferred embodiment of the present invention, the implantable, broadly tubular enclosure has a front tip that is substantially rigid in the erect state. The reservoir is adapted to hold a substantial portion of the fluid needed to transform the tubular portion from its flaccid to its erect state such that the volume of the chamber section increases as the chamber section is transformed from its flaccid to its erect state.
Figure 1 is a side elevational vie~ of one embodiment of the present invention, in use, in its flaccid state;
Figure 2 is a side elevation view of the embodi~nent shown in Figure 1 in its erect state;
- :~287~49 Figure 3 is an enlarged vertical cross-sectional view taken generally along the curve 3-3 in Figure 1;
Figure 4 is a cross-sectional view taken generally along the line 4-4 in Figure 1 of one embodiment in the flaccid state;
Figure 5 is a cross-sectional view taken generally along the line 5-5 in Figure 2 of one embodiment in the ereet state; and ` ~Z87449 Figure 6 is an enlarged cross-sectional view of the valving portion of the prosthesis shown in Figure 3.
Referring to the drawing wherein like reference characters are utilized for like parts throughout the several views, a unitary, inflatable penile prosthesis 10, shown in Figure l, includes an implantable, broadly tubular enclosure 12 sized to be implanted within one corpus cavernosum of the penis. Normally two devices of the kind shown in Figure l are implanted, one in each corpus cavernosum. However, the present invention is adaptable for use with double cylinder designs in which one prosthesis is used to fill both corpus cavernosa. The outer layer of the tubular enclosure 12 is advanta~eously made up of material which is biocompatible. One particularly suitable material for this purpose is silicone, since it is readily accepted by the human body when used with indwelling devices.
The enclosure 12 includes a proximal section 14, a pressurizable medial section 16, and a distal portion 18.
2S Normally the proximal section 14 is positioned in the rear of the corpus cavernosum under the puboischiatic rami. As shown in Figure 3, the proximal section 14 defines a rear fluid reservoir 20. A rigid stabilizer 22 extends rearwardly from the medial section 16 centralLy through the fluid reservoir 20 to a rounded end 26 in contact with the rear tip 24. The stabilizer 22 serves to maintain the shape of the rear fluid reservoir 20 and provide rigidity regardless of the amount of fluid contained therein.
Conveniently the rear tip 24 has a slightly tapered external configuration as a result. A conventional rear --` 1287449 tip extender (not shown) may be provided to lengthen the enclosure 12, if necessary.
The distal section 18 advantageously includes a front tip 25 that is substantially rigid, so as to resist bucXling during intercourse, at least in the erect state.
Advantageously the tip 25 is rigid in both the erect and flaccid states. If desired, the front tip may be made substantially solid.
The medial section 16 defines a pressurizable chamber 28. The medial section 16 is positioned along the length of the enclosure 12 such that it tends to lie medially along the length of the corpus cavernosum and particularly so that it lies substantially in the portion of the corpus cavernosum which is distal of the body plane. Thus, the pressurizable chamber 28 may provide an inflatable hinge, as will be described in greater detail hereinafter~
As shown in Figure 4, the pressuri7able chamber 28 is defined by a tubular portion 30 which is concentrically contained within a tubular sleeve 32. The tubular portion 30 may be formed of two layers includin~ an inner layer or bladder 34 and a substantially non-distensible layer 36.
The non-distensible layer 36 may take a variety of forms, but advantageously it is formed from a tubular section of woven dacron material, such as a prosthetic vascular graft. The inner layer 34 may be formed of a substantially liquid impervious material, such as silicone.
Adjacent proximal ends of the tubular portion 30 and tubular sleeve 32 are anchored to the plug 40 which also secures the distal end of the stabilizer 22, as shown in 12~37449 .
_9_ Fi~ure 3. The plug 40 fills the internal volume of the enclosure 12 with the exception of an axial passageway 42.
On the distal end of the pressurizable chamber 28, the tubular portion 30 and sleeve 32 are anchored to the valve plug 46. Like the plug 40, the valve plug 46 fills a portion of the interior of the enclosure 12. In this way, the intermediate portion of the tubula-r sleeve 32 and portion 30 extend between the plugs 40 and 46 in an unsupported fashion. Thus, when the prosthesis 10 is in a flaccid state, as shown in Eigure 1, the portion 30 and sleeve 32 may tend to neck or sag inwardly.
As shown in Figure 4, the tubular portion 30, in its flaccid state, includes a crimp or fold 48. The crimp 48 provides for extra expansion of the tubular portion 30 in order to completely fill the tubular sleeve 32 in its expanded configuration. Because of the nature of the material of the portion 30, it ~enerally expands in girth to a full tubular configuration, as shown in Figure 5, and then comes to a complete stop after which no further expansion or distension is possible. ~hus the change in volume between the position shown in Figure 4 and the position shown in Figure S wherein the portion 30 is essentially unfolded, is relatively small.
The tubular sleeve 32 may be distensible or non-distensible. In one preferred embodiment it is made of a distensible, stretchable, elastic material such as silicone. With an elastic sleeve 32 the relaxed volume of the sleeve 32 may correspond closely to the flaccid volume of the portion 30 so that the sleeve 32 always conforms closely to the configuration of the portion 30. Moreover, with an elastic sleeve 32, the sleeve 32 elastically ~l28~ 9 resists the expansion of the tubular portion 30 from its flaccid to its erect state.
The valve plug 46, shown in Figure 6, includes a bypass valve 50, an inlet valve 52, and an exit valve 54.
The inlet valve 52 communicates on one end with a manually compressible pump 55 defined within the distal portion 18 of the enclosure 12. The inlet valve 5~ communicates on its proximal end with a radially oriented passageway 58.
The radially oriented passageway 58 communicates with a transverse, radially oriented passageway section 60. The passageway 58 and the section 60 communicate with an axial, lengthwise passageway 62 by way of the annular chamber 63 defined by the sleeve 32~ The passageway 62 extends from the distal portion 18 to the proximal portion 14 in fluid isolation from the pressurizable chamber 28.
It empties into the axial passageway 42 and ultimately into the rear fluid reservoir 20.
Regardless of the state of the portion 30 and sleeve 32, communication through the passageway 62 is always possible. The passageway 62 also communicates with the region 64 between the portion 30 and sleeve 32, but only at the point 66 adjacent the axial passageway 42 and at 25 the point 103 adjacent the axial passageway 63. Thus the fluid within the region 64 may be exhausted rearwardly through the prosthesis 10 into the slot 68 defined in the plug 40 and stabilizer 22.
The outlet valve 54, sho~n in Eigure 6, communicates with the manually compressible pump 56 on the distal end and communicates on the other end with the region surrounding the bypass valve 50. Specifically a continuously open passageway 70 is provided across the bypass valve 50 to the interior of the tubular portion 30.
~`2~3~449 Each of the valves 52 and 54 includes an enlarged housing 72, a coiled spring 74 and a valve member 76. The coiled spring 74 biases the valve member 76A of the valve 54 distally while the coiled spring 74 of the valve 52 biases its valve member 76B proximally. The sealing face 78 of each valve 52, 54 seals on an adjacent transversely oriented ledge 80. The sealing faces 78 of the valves 52 and 54 are concave which encourages formation of a good seal. The valves 52, 54 each include a necked down region 82 in the housing 72 proximate to the ledge 80.
The bypass valve 50 includes a generally conical housing 84 with a proximally extending port 86 and a distally extending seat 88. The seat 88 is generally conical as well and communicates with the passageway 90 that in turn communicates with the passageway 58. A ball 92 is normally seated on the seat 88 closing the passageway 90. One or more extensions 94 defined on the conical housing 84 aligned with the passageway 96 permit generally continuous fluid communication from the passageway 96 to the interior of the tubular portion 30.
~owever, reverse flow into the passageway 90 is normally prevented by the ball 92.
A fillin~ port 44 may enable fluid communication between the exterior of the enclosure 12 and the rear fluid reservoir 20 for fluid insertion. A hypodermic needle may be inserted into the port 44 through a central aperture 47 in the base 49 of the stabilizer 22. When the end of the needle reaches the slot 68, the fluid then flows into the reservoir 20. After the needle is re-tracted the port 44 is filled with a sealant 45.
The prosthesis 10 may be operated in the following fashion. Initially a sufficient amount of fluid, such as ~28'7449 a physiological solution, is loaded into the rear fluid reservoir 20 and tubular portion 30. The fluid may be inletted to the fluid reservoir 20 initially and then pumped to the portion 30 as will be described hereinafter.
In any case, the portion 30 contains sufficient fluid to assume the configuration shown in Figure 4. In the flaccid state the portion may contain at least about 50%
of its capacity and in one illustrative embodiment it contains about 90% of its capacity.
The rear fluid reservoir 20 is filled with at least a substantial portion of fluid needed to permit pumping o the fluid from the reservoir 20 through the pump 56 to fill the added tubular portion 30 volume required to transform from the flaccid state shown in Figures 1 and 4 to the erect, filled to capacity state shown in Figures 2 and 5 wherèin the tubular portion 30 is taut and pressurized. For example, the reservoir 20 may contain from about 20% to 100~ of the fluid needed to transform the portion 30 to its erect state. Advantageously, the reservoir 20 contains from about 50% to about 70% of the fluid needed to transform the chamber 28 from the flaccid to the erect state. Additional fluid volume to pressurize the tubular portion 30 may be stored, for example, in the space 64 between the sleeve 32 and portion 30. Normally it will be necessary for the rear reservoir 20 and other fluid storage volumes to contain slightly more ~luid than that which would be held in the difference in the tubular portion 30 vol-tmes shown in Figures 4 and 5, because it is ~0 necessary to prime the various pumping passageways in order to get sufficient 1uid to the tubular portion 30.
Also, it is desirable to provide additional fluid capacity as a safety factor to insure that an erection can be maintained under all normal circumstances. In any case, the necessary fluid amounts can be easily determined in ~287~a~9 practice by those skilled in the art, and depend on the sizes of the various components utilized.
The prosthesis lO is then implanted within the corpus cavernosum of the patient. This may be done using con-ventional surgical techniques well known in the implanta-tion of inflatable penile prostheses. The proximal section 14 is positioned in the rear region of the corpus cavernosum and the distal section 18 in the distal region of the corpus cavernosum. It may be necessary in certain circumstances to use rear tip extenders for the proximal end in a fashion well known in the art to achieve a correct fit.
In order to operate the implanted prosthesis 20, the user initially compresses the manually compressible pump 56 externally of the penis. The compression of the flexible manually compressible pump 56 forces any fluid contained within the pump 56 into the pressurizable chamber 28~ This is because the pressure increase within the pump 56 forces the valve 54 open allowin~ fluid to flow around the valve member 76A through the passageway 70 past the ball 92 and around an extension 94. The user may continue to successively depress the pump 56 until the pressure within the pressurizable chamber 28 becomes sufficiently great that the valve member 76A no longer unseats from the sealin~ surface 78. At the same time, the compression of the pump 56 seals the inlet valve 52 closed.
Each time the user releases the pump 56, its walls spring back to their original position. This creates suction within the pump 56, opening the valve 52 and drawing fluid into the pump 56. The fluid is drawn from -the reservoir 20 through the passageway 62. When the suction subsides, the valve 52 springs closed.
In the erect or substantially rigid configuration, 5 the tubular portion 30 and sleeve 32 are puffed outwardly slightly from the configuration shown in Figures 1, 3, and 4, to that illustrated in Figures 2 and 5. Moreover, the prosthesis 10 is straight rather than angled or L-shaped.
The sleeve 32 is stretched radially outwardly so as to fit 10 snugly about the tubular portion 30.
In the flaccid state, the prosthesis 10 bends to accommodate to the natural flaccid shape of the penis.
The bending occurs along the pressurizable chamber ~8 15 which essentially acts as a hinge.
To resume the flaccid state after an erection, the valve plug 46 is squeezed externally. As a result of the deformation of the conical housing 84 and seat 88, 1uid 20 is allowed to flow from the pressurizable chamber 28 past the ball ~2 and into the passageway 90. From there the fluid may flow through the passage 60 or the passage 58 to the passageway 62. ~3ecause of the pent up pressure within thè pressurizable chamber 28, the fluid is forced 25 rearwardly through the passageway 62 into the rear fluid reservoir 20 where it is stored for use in the next erection. When the pressure within the chamber 28 has subsided sufficiently, manual actuation of the bypass valve S0 no longer has any effect on fluid outflow from 30 the pressurizable chamber 28 and the prosthesis 10 is in equilibrium. In this state the prosthesis 10 assumes a substantially flaccid configuration and bends with the penis so as to fold along the pressurizable chamber 28.
~l2874~9 ~ ith the present invention the volume of the pressurizable chamber 28 is nonconstant during expansion to erection. This is because at least a portion of the fluid required to achieve the erect state is obtained from sources external of the chamber 28, for example from the rear reservoir 20. Thus, the volume of the chamber 28 increases as the chamber 28 transforms to its erect state.
A fluid volume safety factor may be provided, with the present invention, without increasing the necessary girth of the flaccid prosthesis. This is because additional available volume may be provided without enlarging the medial portion 16 of the flaccid prosthesis.
With the present invention, the pressurizable chamber 28 and thus the prosthesis as a whole may be smaller in the flaccid state. The use of the rear reservoir 20 causes the device to take on a smaller flaccid configuration and to bend easily alon~ the medial portion 16. In addition, the prosthesis may deflate more readily and naturally. This is because the tubular sleeve 32 forces the portion 30 to assume its deflated configuration by pressing the fluid outwardly of the pressurizable chamber 28.
Because the integrity of the fluid passageway 62 remains inviolate and uncrimped, the egress of fluid from the pressurizable chamber 28 is assured and may be carried on in a relatively smooth fashion. Also, because the distension of the portion 30 is minimized, the tendency for faults or creases to block operation of the prosthesis lQ is lessened.
Claims (10)
1. A unitary inflatable penile prosthesis implantable within at least one corpus cavernosum of the penis comprising:
an implantable, broadly tubular enclosure;
a generally tubular pressurizable chamber section defined medially within said enclosure, said chamber section including a substantially nondistensible tubular portion and a tubular sleeve concentric with said tubular portion, said tubular portion being expandable from a flaccid to an erect state when the interior volume of said tubular portion is filled substantially to capacity;
a fluid containing reservoir defined within said enclosure in series along the length of said enclosure with respect to said chamber section;
a manually compressible pump defined within said enclosure in series along the length of said enclosure with respect to said chamber section, said pump adapted for fluid communication with said tubular portion; and a passageway fluidically connecting said reservoir and said pump, said passageway being maintained in fluid isolation from said chamber section, said pump adapted to pump fluid to said tubular portion from said reservoir such that the volume of said chamber section increases as said chamber is transformed from its flaccid to its erect state, wherein said reservoir and said pump are located on opposite sides of said chamber section.
an implantable, broadly tubular enclosure;
a generally tubular pressurizable chamber section defined medially within said enclosure, said chamber section including a substantially nondistensible tubular portion and a tubular sleeve concentric with said tubular portion, said tubular portion being expandable from a flaccid to an erect state when the interior volume of said tubular portion is filled substantially to capacity;
a fluid containing reservoir defined within said enclosure in series along the length of said enclosure with respect to said chamber section;
a manually compressible pump defined within said enclosure in series along the length of said enclosure with respect to said chamber section, said pump adapted for fluid communication with said tubular portion; and a passageway fluidically connecting said reservoir and said pump, said passageway being maintained in fluid isolation from said chamber section, said pump adapted to pump fluid to said tubular portion from said reservoir such that the volume of said chamber section increases as said chamber is transformed from its flaccid to its erect state, wherein said reservoir and said pump are located on opposite sides of said chamber section.
2. A prosthesis according to claim 1, characterized in that the passageway is defined as a narrow channel extending axially along the length of said prosthesis externally of said tubular pressurizable chamber section.
3. A prosthesis according to claim 1, characterized in that the tubular portion crimped in its flaccid state.
4. A prosthesis according to claim 3, characterized in that the crimp extends radially inwardly and is arranged lengthwise with respect to the prosthesis.
5. A prosthesis according to claim 1, characterized in that the region between said tubular portion and said sleeve communicates with said reservoir.
6. A prosthesis according to claim 1, characterized in that said sleeve surrounds said tubular portion.
7. A prosthesis according to claim 1, characterized in that the tubular portion includes an outer layer of non-distensible material and an inner flexible layer.
8. A prosthesis according to claim 1, characterized in that the sleeve is maintained in contact with the tublar portion in both the erect and flaccid states.
9. A prosthesis according to claim 1, characterized by including a manually operable release valve operable from outside said enclosure to allow fluid flow from the chamber section to the reservoir.
10. A prosthesis according to claim 1, characterized by including a relatively rigid stabilizer maintained within the interior of the reservoir.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US705,508 | 1985-02-25 | ||
| US06/705,508 US4590927A (en) | 1985-02-25 | 1985-02-25 | Unitary, inflatable penile prosthesis system |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1287449C true CA1287449C (en) | 1991-08-13 |
Family
ID=24833789
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA000502420A Expired - Lifetime CA1287449C (en) | 1985-02-25 | 1986-02-21 | Unitary inflatable penile prosthesis |
Country Status (5)
| Country | Link |
|---|---|
| US (1) | US4590927A (en) |
| EP (1) | EP0193352B1 (en) |
| JP (1) | JPS61222444A (en) |
| CA (1) | CA1287449C (en) |
| DE (1) | DE3662170D1 (en) |
Families Citing this family (47)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4726360A (en) * | 1986-07-17 | 1988-02-23 | Medical Engineering Corporation | Penile prosthesis |
| US4917110A (en) * | 1986-07-17 | 1990-04-17 | Medical Engineering Corporation | Penile prosthesis |
| US4711231A (en) * | 1986-11-03 | 1987-12-08 | Aaron N. Finegold | Implantable prosthesis system |
| US4823779A (en) * | 1987-05-15 | 1989-04-25 | Medical Engineering Corporation | Penile implant with compensator |
| US4898158A (en) * | 1987-05-15 | 1990-02-06 | Medical Engineering Corporation | Penile implant with improved pressure relief valve |
| US4773403A (en) * | 1987-08-17 | 1988-09-27 | Medical Engineering Corporation | Penile prosthesis |
| US4875472A (en) * | 1987-12-10 | 1989-10-24 | American Medical Systems, Inc. | Flat coil spring penile prosthesis |
| US4881530A (en) * | 1988-01-19 | 1989-11-21 | Medical Engineering Corporation | Penile prosthesis |
| US4895139A (en) * | 1988-08-29 | 1990-01-23 | American Medical Systems, Inc. | Inflatable penile prosthesis with bend release valve |
| US5048510A (en) * | 1988-08-29 | 1991-09-17 | American Medical Systems, Inc. | Inflatable penile prosthesis with satellite reservoir |
| US4995380A (en) * | 1989-11-07 | 1991-02-26 | Medical Engineering Corporation | Penile prosthesis |
| US5010882A (en) * | 1989-11-13 | 1991-04-30 | American Medical Systems, Inc. | Implantable penile prosthesis |
| US5141509B1 (en) * | 1991-08-06 | 1996-01-23 | American Med Syst | Penile prosthesis having means for preventing spontaneous inflation |
| US5263981A (en) * | 1992-04-24 | 1993-11-23 | American Medical Systems, Inc. | Implantable penile prosthesis |
| US5851176A (en) | 1996-07-29 | 1998-12-22 | Mentor Corporation | Pressure-responsive lockout valve and method of use |
| US6533719B2 (en) * | 2000-12-27 | 2003-03-18 | Ams Research Corporation | Diaphragm based spontaneous inflation inhibitor in a pump for an inflatable prosthesis |
| US6730017B2 (en) | 2000-12-27 | 2004-05-04 | Ams Research Corporation | Pressure based spontaneous inflation inhibitor with penile pump improvements |
| US6723042B2 (en) * | 2000-12-27 | 2004-04-20 | Ams Research Corporation | Penile pump with side release mechanism |
| US6991601B2 (en) * | 2002-12-02 | 2006-01-31 | Ams Research Corporation | Implantable pump |
| US7244227B2 (en) * | 2003-03-10 | 2007-07-17 | Ams Research Corporation | Implantable penile prosthesis pump |
| US6808490B1 (en) * | 2003-04-25 | 2004-10-26 | Ams Research Corporation | Penile prosthesis with improved tubing junction |
| US7390296B2 (en) * | 2003-06-06 | 2008-06-24 | Ams Research Corporation | Inflatable penile prosthesis with volume displacement materials and devices |
| KR101032766B1 (en) * | 2003-10-02 | 2011-05-06 | 에이엠에스 리써치 코오포레이션 | Implantable penile prosthesis pump |
| EP1667615B1 (en) * | 2003-10-02 | 2018-11-21 | Boston Scientific Scimed, Inc. | Penile prosthesis devices |
| US7637861B2 (en) | 2004-12-17 | 2009-12-29 | Ams Research Corporation | Implantable penile prosthesis pump |
| US7946975B2 (en) | 2005-04-08 | 2011-05-24 | Ams Research Corporation | Fluid reservoir for penile implant devices |
| US20070175487A1 (en) * | 2006-01-27 | 2007-08-02 | Eid J Francois | Disposable Surgical Drape |
| US8109870B2 (en) | 2006-11-10 | 2012-02-07 | Ams Research Corporation | Inflatable penile prosthesis bypass valve noise reduction |
| US8911350B2 (en) | 2007-10-23 | 2014-12-16 | Ams Research Corporation | Malleable prosthesis with enhanced concealability |
| US8114011B2 (en) * | 2007-10-23 | 2012-02-14 | Ams Research Corporation | Corrugated inflatable penile prosthesis cylinder |
| US8123674B2 (en) | 2007-11-12 | 2012-02-28 | Ams Research Corporation | Corrugated expansion-constraining sleeve for an inflatable penile prosthesis cylinder |
| DK200801306A (en) * | 2008-09-18 | 2010-03-19 | Coloplast As | Apparatus and method for reinforcement of penile cylinders |
| US8097014B2 (en) * | 2008-09-30 | 2012-01-17 | William D. Borkon | Variable rigidity vaginal dilator and use thereof |
| US8702589B2 (en) * | 2008-12-23 | 2014-04-22 | Ams Research Corporation | System to transport components of implantable penile prostheses |
| US7985176B1 (en) | 2010-05-26 | 2011-07-26 | Coloplast A/S | Method of implanting a penile prosthesis |
| US7959556B2 (en) * | 2009-08-27 | 2011-06-14 | Coloplast A/S | Penile prosthesis cap, assembly, and implantation tool |
| US8231521B2 (en) * | 2009-09-22 | 2012-07-31 | Coloplast A/S | Penile prosthesis insertion tool and system |
| US7938770B2 (en) * | 2009-09-22 | 2011-05-10 | Coloplast A/S | Penile prosthesis, penile prosthesis insertion tool and system thereof |
| US8241203B2 (en) * | 2010-02-12 | 2012-08-14 | Fogarty Terence M | Inflatable penile prosthesis with spool valve |
| US9474610B2 (en) | 2010-12-21 | 2016-10-25 | Boston Scientific Scimed, Inc. | Adjustable length rear tip extender for penile prosthesis |
| US9084678B2 (en) | 2012-01-20 | 2015-07-21 | Ams Research Corporation | Automated implantable penile prosthesis pump system |
| US10874516B2 (en) * | 2014-06-27 | 2020-12-29 | Boston Scientific Scimed, Inc. | Implantable penile prostheses |
| US9561107B2 (en) | 2014-12-04 | 2017-02-07 | Coloplast A/S | Base for a penile prosthetic implant and a penile prosthetic system |
| US9549729B2 (en) | 2015-02-06 | 2017-01-24 | Coloplast A/S | System for implanting a penile prosthetic includes a suture and a needle inserted into a tool |
| US9855144B2 (en) | 2015-09-09 | 2018-01-02 | Coloplast A/S | Penile prosthetic with an insertion tool contained inside an inflatable bladder |
| EP3150174B1 (en) | 2015-09-30 | 2021-08-11 | Coloplast A/S | A penile prosthetic with an insertion sleeve attachable to an inflatable bladder |
| EP3357458A1 (en) | 2017-02-02 | 2018-08-08 | Coloplast A/S | Inflatable penile prosthetic system |
Family Cites Families (10)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DE8208210U1 (en) * | 1983-04-21 | Katalinic, Dimitrije, Dr. med., 8501 Oberasbach | Erectable penile prosthesis | |
| US4009711A (en) * | 1976-03-17 | 1977-03-01 | Uson Aurelio C | Penile prosthesis for the management of erectile impotence |
| US4267829A (en) * | 1979-04-11 | 1981-05-19 | American Medical Systems, Inc. | Penile prosthesis |
| US4318396A (en) * | 1980-05-15 | 1982-03-09 | Medical Engineering Corporation | Penile prosthesis |
| US4360010A (en) * | 1980-05-15 | 1982-11-23 | Medical Engineering Corporation | Penile prosthesis |
| US4353360A (en) * | 1980-10-31 | 1982-10-12 | Medical Engineering Corporation | Penile erectile system |
| US4407278A (en) * | 1981-05-15 | 1983-10-04 | American Medical Systems, Inc. | Penile prosthesis with improved fluid control |
| US4399811A (en) * | 1981-08-04 | 1983-08-23 | Medical Engineering Corporation | Implantable penile erectile system |
| US4369771A (en) * | 1981-09-24 | 1983-01-25 | Medical Engineering Corporation | Penile erectile system |
| US4449520A (en) * | 1982-09-02 | 1984-05-22 | Palomar Juan M | Penile prosthesis device |
-
1985
- 1985-02-25 US US06/705,508 patent/US4590927A/en not_active Expired - Lifetime
-
1986
- 1986-02-20 EP EP86301200A patent/EP0193352B1/en not_active Expired
- 1986-02-20 DE DE8686301200T patent/DE3662170D1/en not_active Expired
- 1986-02-21 CA CA000502420A patent/CA1287449C/en not_active Expired - Lifetime
- 1986-02-25 JP JP61040130A patent/JPS61222444A/en active Granted
Also Published As
| Publication number | Publication date |
|---|---|
| JPH0452147B2 (en) | 1992-08-21 |
| DE3662170D1 (en) | 1989-04-06 |
| EP0193352A1 (en) | 1986-09-03 |
| US4590927A (en) | 1986-05-27 |
| JPS61222444A (en) | 1986-10-02 |
| EP0193352B1 (en) | 1989-03-01 |
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| MKLA | Lapsed |