in the following , preferred embodiments of the invention will be described in further details with reference to the drawing in which fig1 shows a telescopic catheter , with a distal 1 and a proximal section 2 . the distal section 1 has a transition end 3 and a proximal guiding end 4 . the proximal section 2 has a transition end 5 and a distal insertion end 6 . the angle between the longitudinal direction of the catheter and the conical erection on the distal section is marked 7 . the angle between the longitudinal direction of the catheter and the conical erection on the proximal section is marked 8 . the transition end of the proximal section has an outer diameter which is higher than the remainder of the proximal section ( the difference a ). the transition end of the distal section has on outer diameter which is smaller than the remainder of the proximal section ( the difference b ). fig3 shows the principle of another embodiment of a catheter 30 according to the invention . the distal section 1 ( the outer section ) displays a decreased outer circumference 31 in the transition , whereas the proximal section 2 ( the inner section ) displays an increased outer circumference 32 in the transition . the proximal end of the distal section 33 is here cut to allow for a smooth transition point . by adding cylindrical parts such as the decreased outer circumference 31 and the increased outer circumference 32 the surface of the transition sections is increased , thereby creating a larger area wherein the distal section and proximal section can couple together . fig4 shows another embodiment 40 of the catheter , which discloses one way to obtain decreased elasticity in the transition end ( the distal end ) of the proximal section . the embodiment of fig4 is identically to the embodiment of fig3 , however , the thickness of the wall has been doubled by insertion of an additional tube 41 , which stabilizes the transition and provides decreased elasticity . fig5 shows another embodiment 50 of the catheter , which discloses one way to obtain decreased elasticity in the transition end ( the distal end ) of the proximal section . here , the thickness of the end wall of the distal section 1 has been increased by molding the tube with a thicker wall 52 . fig6 shows another embodiment 60 of the catheter , which discloses one way to obtain decreased elasticity in the transition end ( the proximal end ) of the distal section . here , the thickness of the end wall of the distal section 1 has been increased by molding the tube with a thicker wall 61 on that part . fig7 shows another embodiment 70 of the catheter , which discloses a combination of fig4 shows another embodiment 40 of the catheter , which discloses one way to obtain decreased elasticity in the transition end ( the distal end ) of the proximal section . the embodiment of fig4 is identically to the embodiment of fig3 , however , the thickness of the wall has been doubled by insertion of an additional tube 41 , which stabilizes the transition and provides decreased elasticity . and fig5 shows another embodiment 50 of the catheter , which discloses one way to obtain decreased elasticity in the transition end ( the distal end ) of the proximal section . here , the thickness of the end wall of the distal section 1 has been increased by molding the tube with a thicker wall 52 . : an increased wall - thickness in the transition end of both the distal section and the proximal section . fig8 shows another embodiment 80 of the catheter , which discloses transition with a third element . that is , the thick black line is the distal section 81 . the outer circumference of the distal section decreases ( going from left to right ), is followed by a flat segment , and is thereafter pointed to provide for a smooth transition point . the proximal section 82 is the hatched line . the outer circumference of this proximal section increases ( going from right to left ). the two sections can be pulled together . however , a third element 83 is positioned between the decrease in outer circumference of the distal section and the increase in outer diameter of the proximal section . fig9 illustrates another embodiment 90 of the catheter and the transition between the distal section 1 ( left ) and the proximal section 2 ( right ). the distal section is cut to be pointed towards the end ( the proximal end ) and fits towards the regular tubular part of the proximal section . fig1 illustrates another embodiment 100 of the catheter , which discloses the transition between the distal section 101 ( left ) and the proximal section 102 ( right ). the distal section is cut to be pointed towards the end ( the proximal end ) and fits towards the part of the proximal section undergoing an increase in outer circumference . the inner circumference of the tip in the transition end of the distal part is bigger than the outer circumference of the proximal section so that a coating on the proximal section is not damaged when the tip passes this section during expansion of the catheter . fig1 illustrates another embodiment 110 of the catheter , which discloses a bulb 111 on the proximal tube , just proximally to the transition part . fig1 illustrates another embodiment 140 of the catheter according to the invention . here a third element 141 is placed on the outside of the transition part of the distal section . the third element is formed as a ring having an outer circumference of the same size as the outer circumference of the distal section . the third element has a proximal face which tapers with the same angle as the proximal end of the distal section . fig1 illustrates the forces between the distal section 1 and the proximal section as described earlier when the catheter is in its expanded configuration . the sections are only shown schematically and solid lines indicate their walls . the area between the tapering part of the two sections defines the conical contact zone 150 . although dry catheters are easier to engage in a frictional lock with each other , a hydrophilic catheter may also engage into a frictional lock when first and second conical faces 151 , 152 of the two sections are pulled against each other in the contact zone 150 . high friction may thus be provided when a first angle α 1 of the first conical face 151 ( relative to the axis of the distal section ) and a second angle α 2 of the second conical face 152 ( relative to the axis of the proximal section ) are less than 40 °. low friction is created when the first angle α 1 and the second angle α 2 are between 90 ° and 110 °. fig1 - 21 shows one embodiment of an expandable catheter 151 . fig1 shows an enlarged view of section xviii in fig1 and fig2 and 21 shows enlarged views of sections xx and xxi , respectively , in fig1 . fig1 a and 19 b shows respectively a distal section and a proximal section of fig1 . the sections illustrated in fig1 a and 19 b are shown in an exploded view along axis a - a . the catheter 151 is operable between a collapsed configuration , shown in fig1 , for storage and transportation and an expanded configuration , shown in fig1 , for draining fluid from a body via a conduit 153 which extends axially in a longitudinal direction , indicated by arrow 179 , from a proximal end 165 to an opposite distal end 171 . the catheter comprises a proximal section 2 , adapted to be fully inserted into a urinary channel of the body ( not shown ) and forming a proximal part of the conduit which part extends axially between the proximal end 165 and a first transition end 164 of the proximal section 2 . the catheter further comprises a distal section 1 , adapted to be at least partially inserted into the urinary channel ( not shown ) and forming a distal part of the conduit which part extends axially between a second transition end 170 of the distal section 1 and the distal end 171 . the first transition end 164 is dimensioned to enable its positioning inside a receiving portion of the distal part of the conduit 153 to enable axial movement of the sections relative to each other to operate the catheter 151 between the collapsed configuration and the expanded configuration of the catheter , wherein the sections comprise cooperating coupling structures to support the catheter in the expanded configuration . beside the proximal section 2 and the distal section 1 , the catheter 151 is also provided with a connector 152 . together the two sections and the connector forms the conduit 153 extending axially along the axis a - a . the proximal section is formed of a proximal catheter tube 154 , defining a first duct 155 , and a first sleeve 156 having a base 157 , a shaft 158 , a head 159 and a second duct 160 extending there through . the first transition end 164 and the proximal end 165 define the axial extent of the proximal section . the head and the shaft of the first sleeve are inserted into the first duct of the proximal catheter tube and thereby form the proximal section . in this configuration the first duct and the second duct together defines a proximal part of the conduit . to avoid separation the proximal catheter tube and the first sleeve are welded together . other means for joining exists , such as gluing . additionally or alternatively the outer circumference of the shaft and the head of the first sleeve may be larger than the inner circumference of the proximal catheter tube whereby the tube will grip tightly around the first sleeve . as can be seen the first proximal section have an outer surface with a first surface portion 181 with a first circumference , which when seen in the longitudinal direction is followed by a second surface 182 having a second circumference which is larger than the first circumference . a third surface portion 183 follows the second surface portion . the third circumference of the third surface portion is smaller than the second surface portion . by providing smooth transitions between the first , second and third surface portion a bulb 161 is provided on the outer surface of the proximal catheter tube . in practice the bulb 161 is provided by the head 159 , which is formed with an enlarged surface portion , which has a larger circumference than the shaft 158 . the head will thereby radially expand the proximal catheter tube and create the bulb 161 . by forming a fourth surface portion 184 on the base 157 with a circumference which is larger than the circumference of the third surface portion , a first rim 162 is provided when the proximal catheter tube and the first sleeve are joined to form the proximal section . a slot 163 is thereby formed between the second surface portion , i . e . the bulb 161 , and the fourth surface portion , i . e . the first rim 162 . the distal section 1 is formed of a distal catheter tube 180 , defining a third duct 165 and a second sleeve 166 having an outer tapering surface 167 , an incision 168 and a fourth duct 169 . a second transition end 170 and a distal end 171 define the axial extent of the proximal section . the circumference of the fourth duct of the second sleeve is smaller than the circumference of the third duct of the distal catheter tube . when they are joined this relation provides a second rim 172 . a key 173 , provided by a fifth surface portion 185 , is thus defined between the second rim and the second transition end 170 . in order to provide as smooth transition to from the proximal section to the distal section when the catheter is in its expanded configuration the outer surface of the second sleeve has an eighth surface portion shown as the outer tapering surface 167 , which decreases towards the second transition end . the distal catheter tube 180 and the second sleeve 166 are joined together by inserting the incision into the third duct . the area of the distal catheter tube contacting a ninth surface portion 187 of the incision thereto is then welded together to fix the distal catheter tube and the second sleeve to each other . in this configuration the third duct and fourth duct together forms the distal part of the conduit . when the catheter is moved from its collapsed configuration , as shown in fig1 , to its expanded configuration , as shown in fig1 , the key 173 engages with the slot 163 and thereby couples the proximal section and the distal together in the expanded configuration . the illustrated catheter assembly is especially advantageous for use with expandable catheters having a hydrophilic coating ( not shown ). as can especially be seen in fig2 and 21 a gap 175 is provided between the surface of the key and the surface of the slot . a gap of approximately the same size is furthermore provided when the key is displaced along the first surface portion 181 of the proximal section on the other side of the bulb 161 from the slot . the gap provides radial clearance between the key and the first surface portion which avoids that the hydrophilic coating is scraped off the proximal section when the sections are axially displaced . furthermore , the hydrophilic coating will fill out the gap and the surface tension of the hydrophilic coating will advantageously center the key evenly around the first surface portion . as can be seen the axial extent of the key is slightly longer than the extent of the slot . this will jam the key between the first rim and the sloping surface 174 of the bulb 161 . advantageously this will seal off the gap whereby the mucosa of the urethra , which is very flexible , i . e . the mucosa follows the curvature of the urinary catheter , may be prevented to enter the gap wherein the mucosa otherwise could get caught between the key and slot and consequently get squeezed causing pain and maybe even tear the mucosa . as the circumference of the key 173 limits the outer circumference of the proximal catheter tube the key typically only extends a few millimeters . thus , to provide secure engagement of the proximal and distal section and to avoid that they unintentionally are pulled apart it is desirable that the first rim 162 and the second rim 172 contacts each other in a large surface area . furthermore it is desirable that the edges of the first and second rim and are well defined , and preferably has a small rounding in order to prevent that the rounding surface may act as guides which may push the rims key over the fourth surface portion 184 . in order to properly seal the gap the second transition end 170 , which abuts against the bulb 161 is exerting an axially directed force f 1 onto the distal sloping surface 174 of the bulb . for secure seal the sloping surface will react with an equally opposite axially directed force f 2 . however should the size of the force f 1 become too large the bulb will collapse , which will result in that the distal and proximal section will be uncoupled and the catheter will move from its expandable configuration to its collapsed configuration . in order to prevent this the distance between the radial extending distance from the surface 177 of the slot to the maximal radial extending distance of the bulb , a , should be at least two times the length than the radial extending distance from the surface of the slot to the surface of the key , b , i . e . a ≧ 2 * b . the distance b corresponds to the size of the gap 175 seen transverse to the longitudinal direction . it should however be understood that this relation may vary depending on the material of respectively the key and the bulb and the type of coating used to coat the catheter . furthermore , the angular slope of the distal sloping surface 174 to the axis a - a will affect the required size of f 1 in order for the sections to uncouple and the chance that the mucosa may get squeezed between the second transition end and the sloping surface . furthermore such relations will also depend on the types of materials used . one type of materials used to produce the catheter may be rigid polyurethane , such as estane ete x1014 for the distal section 1 and the first sleeve 156 . the proximal catheter tube 154 may for example be formed of soft polyurethane , such as estane 58212 . when used the expandable catheter is moved from its collapsed configuration into its expanded configuration . the proximal end 165 is inserted into the urethra followed by the proximal section 2 and the distal section 3 until urine start flowing through the conduit . the catheter is usually inserted by into the urethra by gripping the connector part 152 between two or more fingers of one hand and guiding the proximal end into the urethra with the other hand . the urine will flow through the through a hole 178 formed in the proximal section 2 close to the proximal end , into the conduit and then through the conduit in mainly a longitudinal direction parallel to the longitudinal extent , shown as axis a - a in fig1 - 19 b , of the conduit , as indicated by the arrow 179 in fig1 and 16 , and out through the connector 152 . although the embodiment illustrated in fig1 a - 18 is especially suited for hydrophilic - coated catheters it may be used for other types of coated catheters known to the skilled person , for example gel coated catheters . fig2 illustrates another embodiment of the coupling structures of a catheter 200 according to invention . the figure shows seen in longitudinal section the area of the catheter in where the proximal section 2 and the distal section 1 couples together in the catheters expanded configuration . the proximal section is formed of a proximal catheter tube 201 wherein the neck 202 of a sleeve 203 is inserted . in order to fix the two parts together a weld has been provided between the neck and the inner surface of the proximal catheter tube . a first transition end 204 is defined at the distal end of the sleeve 203 the distal section is formed of a one - piece molded catheter tube 205 . the distal section have a first outer surface portion 206 having an increasing circumference seen from a second transition end in the longitudinal direction towards a distal end ( not shown ). the inner surface of the distal section is , seen in order from the second transition end , provided with a first 208 , second 209 , third 210 and fourth 211 surface portions . the first and third surface portions have a smaller circumference than the second and fourth surface portion . as can be seen in fig2 the second surface portion thus forms a slot 216 defined by the first and third surface portion . corresponding to the inner surface portions of the distal section there is provided a fifth 212 , sixth 213 , seventh 214 and eighth 215 surface portions on the outer surface of the proximal part . the fifth surface portion has a circumference , which is smaller than the circumference of the first surface portion , and the seventh surface portion has a circumference , which is smaller than the circumference of the third surface portion . the sixth surface portion has a circumference , which is smaller than the second surface portion but larger than the circumference of the fifth and seventh surface portion . the eighth surface portion has a circumference which is smaller than the circumference of the fourth surface portion but larger than the circumference of the third surface portion . the sixth surface portion is advantageously provided as an annular flange being flexible transverse to the axis of the catheter . this allows for the flange to function as a key 217 , which engages with the slot when the catheter is in its expanded configuration . by being flexible the key will easily move past the third surface portion . furthermore , as the eighth surface portion has a circumference which is larger than the circumference of the third surface portion a stop is provided as a protruding rim 218 , which prevents the distal section and the proximal section from being pulled apart . the test is performed as a tensile test in a standard test machine as a lloyd lr 5k . the desired konical connection is placed in the tensile test machine and the force is measured when the parts are pulled apart . the maximum load is registered . materials in the test is estane ete x1014 for the outer tube and estane 58212 for the inner tube ( see table 1 ). the default configuration takes about 12 n to pull apart ( fig2 , i ). however , when the thickness of the distal section is doubled ( for example to 0 , 7 mm ) it takes about 20n to pull the two sections apart ( fig2 , ii . fig5 shows another embodiment 50 of the catheter , which discloses one way to obtain decreased elasticity in the transition end ( the distal end ) of the proximal section . here , the thickness of the end wall of the distal section 1 has been increased by molding the tube with a thicker wall 52 . if the thickness of the wall of the proximal section is increased to 1 . 6 mm , the force required to pull the two sections apart goes from 12 n to about 30 n ( fig2 , iii . fig3 shows the principle of another embodiment of a catheter 30 according to the invention . the distal section 1 ( the outer section ) displays a decreased outer circumference 31 in the transition , whereas the proximal section 2 ( the inner section ) displays an increased outer circumference 32 in the transition . the proximal end of the distal section 33 is here cut to allow for a smooth transition point . by adding cylindrical parts such as the decreased outer circumference 31 and the increased outer circumference 32 the surface of the transition sections is increased , thereby creating a larger area wherein the distal section and proximal section can couple together .) a synergistic effect was observed when the thickness of both the proximal and the distal transition was increased ( doubled as described above ). then , a force of about 60 n was required to pull the sections apart ( fig2 , iv , fig6 shows another embodiment 60 of the catheter , which discloses one way to obtain decreased elasticity in the transition end ( the proximal end ) of the distal section . here , the thickness of the end wall of the distal section 1 has been increased by molding the tube with a thicker wall 61 on that part ). in this example , sufficient endurance of the transition between the proximal section and the distal section in an expanded catheter is obtained by increasing the wall thickness . as clearly shown in fig3 shows the principle of another embodiment of a catheter 30 according to the invention . the distal section 1 ( the outer section ) displays a decreased outer circumference 31 in the transition , whereas the proximal section 2 ( the inner section ) displays an increased outer circumference 32 in the transition . the proximal end of the distal section 33 is here cut to allow for a smooth transition point . by adding cylindrical parts such as the decreased outer circumference 31 and the increased outer circumference 32 the surface of the transition sections is increased , thereby creating a larger area wherein the distal section and proximal section can couple together . a doubling of the wall thickness is obtained by inserting an additional tube inside the proximal tube ( in the distal end , the transition end ). however , during molding of the catheter tube , the inner - wall can be reinforced by increasing the wall - thickness — such increased wall - thickness is clearly illustrated in fig4 shows another embodiment 40 of the catheter , which discloses one way to obtain decreased elasticity in the transition end ( the distal end ) of the proximal section . the embodiment of fig4 is identically to the embodiment of fig3 , however , the thickness of the wall has been doubled by insertion of an additional tube 41 , which stabilizes the transition and provides decreased elasticity . the same principle as described for the inner - wall , can be applied to the outer - wall ( the distal section ). as shown in fig5 shows another embodiment 50 of the catheter , which discloses one way to obtain decreased elasticity in the transition end ( the distal end ) of the proximal section . here , the thickness of the end wall of the distal section 1 has been increased by molding the tube with a thicker wall 52 . the thickness of the wall of the distal section is increased while the inner circumference of the tube is decreased . from the outside it appears as a straight line , giving a smooth feeling to this reinforcement . when the outer circumference of the proximal section has reached its minimum ( that is , the circumference the rest of the tube has ) the decrease in outer circumference of the distal section starts , ending in a smooth transition . however , to obtain the highest pull - force , as disclosed in the example above , a combination of decreased elasticity of both the inner - and outer tubes is provided in the transition , only . such combination is illustrated in fig6 shows another embodiment 60 of the catheter , which discloses one way to obtain decreased elasticity in the transition end ( the proximal end ) of the distal section . here , the thickness of the end wall of the distal section 1 has been increased by molding the tube with a thicker wall 61 on that part . in one embodiment , the wall thickness of the distal section increases while the inner circumference of the tube decreases . the decrease in inner circumference of this distal section is matched with an increase in outer circumference of the proximal section . however , during this increase in outer circumference of the proximal section the inner circumference is kept constant . hereby , both of the sections comprise reinforced transition parts . as illustrated in fig7 shows another embodiment 70 of the catheter , which discloses a combination of fig4 shows another embodiment 40 of the catheter , which discloses one way to obtain decreased elasticity in the transition end ( the distal end ) of the proximal section . the embodiment of fig4 is identically to the embodiment of fig3 , however , the thickness of the wall has been doubled by insertion of an additional tube 41 , which stabilizes the transition and provides decreased elasticity . fig5 shows another embodiment 50 of the catheter , which discloses one way to obtain decreased elasticity in the transition end ( the distal end ) of the proximal section . here , the thickness of the end wall of the distal section 1 has been increased by molding the tube with a thicker wall 52 . fig5 shows an increased wall - thickness in the transition end of both the distal section and the proximal section . the decreased elasticity in the transition can effectively be provided to both sections through a third element . this element will become trapped between the two sections , and provide the endurance needed . an example is a third element made of estane x4995thermoplastic elastomer . in this case , both sections shall endure full expansion / compression in order to separate . here , the material is placed between the two sections ( fig8 ). however , as illustrated in fig1 , this third material can be placed on the outside of the tubes as well . it is important to provide a smooth transition point . especially , the actual point of transition , that is where mucosal exposure to the proximal section stops and mucosal exposure to the section begins . as illustrated in fig8 shows another embodiment 80 of the catheter , which discloses transition with a third element . that is , the thick black line is the distal section 81 . the outer circumference of the distal section decreases ( going from left to right ), is followed by a flat segment , and is thereafter pointed to provide for a smooth transition point . the proximal section 82 is the hatched line . the outer circumference of this proximal section increases ( going from right to left ). the two sections can be pulled together . however , a third element 83 is positioned between the decrease in outer circumference of the distal section and the increase in outer diameter of the proximal section . one such transition can be obtained by cutting the proximal end of the distal section in a pointed angle . however , as illustrated in fig9 , this pointed angle can fit closely to the segment of the proximal section where the outer diameter is increasing . obtained hereby is that the outer diameter of the regular tubular segment of the proximal section is smaller than the inner diameter of the proximal end of the distal section . the coating of the catheter is not damaged during pulling the two sections together during expansion of the catheter . an alternative is illustrated in fig1 illustrates another embodiment 100 of the catheter , which discloses the transition between the distal section 101 ( left ) and the proximal section 102 ( right ). the distal section is cut to be pointed towards the end ( the proximal end ) and fits towards the part of the proximal section undergoing an increase in outer circumference . the inner circumference of the tip in the transition end of the distal part is bigger than the outer circumference of the proximal section so that a coating on the proximal section is not damaged when the tip passes this section during expansion of the catheter . fig1 illustrates another embodiment 110 of the catheter , which discloses a bulb 111 on the proximal tube , just proximally to the transition part . . here , a bulb , or a circular protrusion is provided on the proximal section . this bulb will ‘ lift ’ the mucosa to avoid contact with the point of transition . furthermore , such bulb will act as a mechanical lock between the distal and the proximal section of the catheter allowing passage in one direction but not in the other . the rigidity of a tube is a function of the design ( form and circumference ) and material properties such as e - modulus or for very soft materials the hardness . for a male person it is important that the proximal part of the catheter — the part that when inserted protrudes from the bladder to the pelvic floor — is soft and flexible in order to fit the curvature of the urethra . the rigidity must be low . at the same time the proximal part must have good kinkability . in the contrary hereto , the distal part should be more rigid to enable easy insertion by avoiding that the catheter bends before the opening of the urethra ( meatus ). the kinkability of the distal part is typically not critical as it can be controlled and monitored by the user . estane ete x1014 is the preferred material for the distal part and estane 58212 is the preferred material for the proximal part . ete 60dt3 is an example of material for the distal part with the lowest acceptable e - modulus — see table 1 for data for different materials are mentioned . a length of 11 cm is cut from the middle of the catheter . the catheter is placed in water at a temperature of 23 ° c . for 30 sec . the catheter is then placed in an adapter situated on the tensile test machine . the tensile machine is started and the force to compress the catheter is logged . fig1 shows the force applied to a typical distal catheter section . the abscissa indicates the compression of the section in millimeters ( extension , mm ) and the ordinate indicates the load force applied in n . as illustrated in fig1 , compression of this typical distal section with a high e - modulus results in a linear compression with the force applied . however , at a certain point ( 15 n ), the section kinks , and the force needed for further bending is low . fig1 shows the force applied to a typical proximal catheter section as described . this elastic section will bend almost proportionally with the force applied . the abscissa indicates the compression of the section millimeters ( extension , mm ) and the ordinate indicates the load force applied in n . as illustrated in fig1 , compression of this typical proximal section with a low e - modulus results in a constant bending of the section with a constant force . the curve in fig1 rises steeply from 0 to 2 n during the first four millimeters of compression of the proximal catheter section . after the first four millimeters the curve flattens , indicating that the proximal section has bent as it still exerts a load of approximately 2 n . thus , to provide a distal section and a proximal section so that the first longitudinal directed force required for moving the catheter from an expanded position to a collapsed position is larger than the second longitudinal directed force required for at least one of the proximal section and the distal section to bend , the first longitudinal directed force is chosen to be above 2 n , which is the second longitudinal directed force . i . e . the coupling structures provided when the catheter is in its expanded configuration needs to be rigid enough to resist a load of at least 2 n . preferably the coupling configuration is dimensioned so that it may resist even higher loads , such as 3 - 10 n . alternatively , keeping in mind that the push - in force required to insert the catheter into the urethra is approximately 1 n , the proximal and distal sections can be provided so that the first longitudinal directed force required for moving the catheter from an expanded position to a collapsed position is smaller than the second longitudinal directed force required for at least one of the proximal section and the distal section to bend , wherein the coupling structures are dimensioned so that the first longitudinal force required is between 1 and 2 n , especially between 1 , 5 n and 2 n and particularly around 1 , 7 n .
a catheter includes a proximal section that is inserted into and telescopically movable relative to a distal section . a proximal end of the proximal section is insertable into a urethra of a user and the distal section provides a discharge conduit for urine . the proximal section includes a rear portion , and an exterior surface of the rear portion diverges away from the proximal end to provide a diverging rear transition section that is wider than the proximal end of the proximal section . the distal section includes a front portion and an interior surface of the front portion converges to an opening formed in a front transition end , the opening is narrower than the diverging rear transition section of the proximal section .