there is a continuing need for improved medical devices and methods to meet some or all the following objectives . an objective may be to reduce cost . cost reduction may be particularly important in recent years where it is clear for safety and sanitary reasons that many devices used in the vasculature should be single use devices . devices , even if performing a function in some improved manner , will not be widely used if they are considerably more costly than the alternatives available . another objective may be ease of use and simplicity of understanding . ease of use and simplicity can encourage device adoption and use by medical personnel . they can also tend to keep cost low . another objective may be to provide devices that entail procedures with which the medical profession is already familiar . by doing so , the skills that have been learned from previous experience can continue to have applicability . another objective relates to the effectiveness and thoroughness with which the device performs , such as blockage removal and vessel occlusion . for example , it is generally important that a maximum amount of the blockage be removed , recognizing that no device is likely to provide one hundred percent removal . another objective concerns safety — a matter , which is often so critical as to trump the other considerations . it is generally important to avoid tissue trauma . in many circumstances , it is critically important to , for example , avoid breaking up a blockage in a fashion that leads to flushing elements of the blockage throughout the body such as by damaging the blood vessels by applying excess pressure on the vessel wall in an attempt to fully occlude the vessel so that blockages can be removed and debris can be prevented from flushing downstream . a goal of the devices disclosed herein is to do just that : provide effective occlusion of a blood vessel to remove blockages and prevent debris from flushing downstream in a manner which does not damage the vessel wall in doing so . there are often trade - offs in design considerations to achieve the above interrelated objectives . extreme simplicity and a very simple procedure might over compromise safety . addressing all of these considerations often calls for some trade - off between the objectives while maintaining the effectiveness and doing so safely . fig1 is an illustration of a prior art occlusion device or funnel catheter 100 in which the proximal end 202 of the tubular mesh braid 200 is attached to the distal aspect of the outer sleeve 194 and the distal end 204 of the tubular mesh braid 200 is attached to the distal aspect 198 of the inner sleeve 196 . in the contracted or non - deployed configuration , as illustrated in fig1 , the tubular mesh braid 200 covers the distal aspect 196 of the inner sleeve 196 . the catheter 100 is essentially in a typical configuration of a standard catheter , albeit with an outer sleeve 194 and inner sleeve 196 comprising the catheter wall . an impervious coating 216 covers the tubular mesh braid 200 , but there may be areas of various porosity 214 in which there is no membrane which serves to enhance the expansile characteristics of the braid 200 by providing areas that are not restricted from expanding because of the elastomer . fig2 is an illustration of a prior art device 100 placed into a blood vessel bv and with the inner sleeve 196 withdrawn . withdrawal of the inner sleeve 196 may cause the flexible tubular mesh braid 200 to buckle in a predetermined manner because of the manner in which the tubular mesh braid 200 was formed so that the tubular mesh braid 200 creates a funnel shape on the distal catheter . the margins of the funnel tip expand to contact the blood vessel wall 210 with a predetermined amount of radial force to occlude blood flow . the length 212 of the wall contact of the margin of the tubular mesh braid 200 may also be important in assisting the occlusion of blood flow . as well , the tubular mesh braid 200 may comprise a coating or a membrane 216 that is essentially impervious to blood but may comprise a variable porosity region 215 in a portion of the braid . this variable porosity region 215 can allow some fluid communication to the space between the inner and outer portions of the tubular mesh braid 200 when the tubular mesh braid is deployed in a funnel shape and can assist in the expansion of the tubular braid as there is less elastomer on the braid , hence less restriction to expansion . the variable porosity may also prevent a vacuum from forming within the folded more or less impervious braid that may prevent it from expanding correctly into a funnel shape . however , in cases with an exaggerated systolic blood pressure of 160 mm hg or in a larger vessel with exaggerated flow such as the carotid or renal arteries , the outward radial force and the length of braid contacting the vessel wall may not be sufficient to arrest the blood flow on a consistent basis . by providing an outward radial force adequate to arrest blood flow , the outward radial force may cause compression of the vessel wall 210 , damaging the wall 210 similar to the forces exerted by balloon inflation which is known to damage the wall and result in restenosis . hence , there may be a need for improved occlusion devices which do arrest blood flow in cases of exaggerated systolic blood pressure or exaggerated high flow states on a consistent and reliable basis , but without exerting an undue or exaggerated amount of force on the vessel wall to do so . moreover , there may be a dilemma with utilizing an outward radial force as the primary means of arresting blood flow as the optimal radial force to arrest blood flow varies as the optimal amount or size of the expanded funnel tip to arrest flow may vary in different sized vessels . the radial force and the size of the funnel tip will be different in a 2 mm coronary artery than in a 6 mm carotid artery and even still different in a 9 mm iliac artery . hence , for different sized vessels , arresting the flow may demand the use of funnel tips with different sizes and different radial forces and different length of the wall contacting surface of the tubular mesh braid 200 . this need for different sizes may create a situation in which it may be difficult to arrest flow over a continuum of sizes and flow situations , which can occur within a single vascular distribution as is the case in the lower extremity , with one design and one size of funnel tip . with the prior art occlusion device 100 , while the funnel tip may oppose and contact the wall over a spectrum of sizes , the ability to occlude over this spectrum of sizes may be limited and may necessitate funnel tips sized specifically for the vessel size . the radial pressure exerted on a 2 mm diameter vessel will be greater than the radial pressure exerted on a 6 or 9 mm diameter vessel . as well , because of the different blood pressures in different patients and different flow rates in different arteries within the same patient , devices should be constructed to provide a greater force than is typically needed so to address the worst possible case which is elevated blood pressure and flow although most cases would not demand it . hence , there may be a need for improved occlusion devices which do arrest blood flow over a range of vessel sizes with an optimized funnel tip which provides radial force sufficient to contact the wall but insufficient radial force to damage the wall . meeting these needs can be accomplished by adding one or more features to the prior art occlusion device to improve upon it so that the occlusion device will arrest flow in cases of exaggerated systolic blood pressure , exaggerated high flow , and over a range of different sized arteries . the sealing or occlusion efficiency of the prior art device can be summarized by the formula : occlusion efficiency of prior art occlusion device = radial force of braid * length or area of contact . hence , the longer the length ( greater area of contact ), the less radial force may be needed to occlude . fig3 is an illustration of an occlusion device or funnel catheter 100 a in accordance with embodiments of the present disclosure in an undeployed or contracted configuration . fig4 is an illustration of the same occlusion device 100 a in a deployed or expanded configuration in the blood vessel bv . the occlusion device 100 a can solve the problem of the prior art occlusion device 100 and can arrest blood flow completely irrespective of the systolic blood pressure or the amount of flow within the vessel . the occlusion device 100 a may comprise a catheter with an inner sleeve 196 , an outer sleeve 194 , and a length of tubular mesh braid 200 in which the proximal end 202 of the tubular mesh braid 200 is attached to the distal aspect of the outer sleeve 194 and the distal end 204 of the tubular mesh braid 200 is attached to the distal aspect of the inner sleeve 196 . as with the prior art occlusion device 100 , the occlusion device 100 a may be constructed so that the funnel tip contacts the vessel wall location 212 with a radial or outward force and with a length of contact with the vessel wall location 212 sufficient to arrest blood flow in most instances . in addition to the two features present in the prior art device 100 to occlude flow , the current occlusion device 100 a also comprises a distinct coating or membrane free portion 215 of the tubular mesh braid 200 in addition to the coated or membrane containing section 216 . fluid or blood may flow freely though this coating free or membrane free section 215 of the tubular mesh braid , as indicated by the arrows 217 , and by doing so will enhance the expansion of the wall contacting segment 212 of the tubular mesh braid 217 by adding the transmitted blood pressure to the outward or radial force of the funnel tip as demonstrated by the arrows 218 so that a seal is achieved no matter the systolic blood pressure , flow state of the vessel or the size of the vessel . the transmitted blood pressure may be additive to the inherent radial outward force utilized to expand a significant length of the funnel tip against the wall as the transmitted blood pressure essentially presses the impervious portion of the tubular mesh braid against the vessel wall . this added pressure can be summarized by the formula : occlusion efficiency of current occlusion device = radial force of braid * area of contact + nominal transmitted blood pressure * area of contact hence , the sealing ability of the current occlusion device 100 a can be a reflection of a combination of the radial force of the braid , the length of the impervious wall contact portion , and the transmitted blood pressure . it can be important to recognize that the coating or membrane free or open portion of the tubular mesh braid 200 should be sized so that a portion of the coated or membrane comprising the impervious portion of the tubular mesh braid 200 is not compromised and that the length of contact of this portion to the wall is maximized while also providing a distinct segment of the tubular mesh braid 200 that allows ingress and egress of fluid or blood . experiments have demonstrated that the optimal length of the open or membrane devoid portion is between 30 - 40 % of the entire length of the tubular mesh braid 200 to accommodate a wide range of vessel sizes , although the ranges could vary between 20 - 60 % and even 3 - 80 % for different or specific situations . actual overall braid length optimally for 2 - 6 mm vessels may be 1 . 6 cm with the coated or membrane containing section comprising 1 . 1 cm and the membrane or coating devoid portion comprising 0 . 5 cm . in larger vessels , the measurement may increase , but the approximate ratios will remain . this optimized length provides proper buckling of the braid 200 to form a funnel , proper ingress and egress of fluid so that the funnel tip expands and contracts easily , promptly , and without difficulty and also provides enough length of contact with the vessel wall so that the device occludes flow in any situation . because of the addition of these important features of providing an optimized section of the braid which does not comprise a membrane or coating to the prior art , the current devices can function consistently to arrest blood flow in blood vessels no matter the blood vessel size , the systolic blood pressure or the flow state of the vessel . as the systolic blood pressure is elevated , a corresponding pressure increase can be transmitted to the inside of the elastomeric coated braid through this section of uncoated braid to press it against the arterial wall insuring a proper seal and occlusion over varying blood pressures . experiments have demonstrated that the present occlusion device 100 a can provide a nominal radial force against the blood vessel wall which is significantly augmented by the contribution of the patient &# 39 ; s own blood pressure which is transmitted through the specific section of the braid 200 which is devoid of a membrane or coating . a 1 . 6 cm tubular mesh braid was constructed with 0 . 005 ″ diameter nitinol wire and bonded to inner and outer tubular catheters and a silicone elastomer was applied over 1 . 1 cm of length maintaining a 0 . 5 cm length devoid of the elastomer . this arrangement caused the braid to buckle properly and form a funnel shape when the inner and outer catheter members were translated relative to one another . compressive unloading measurements , which are reflective of the outward radial force of the device , were performed and the results are presented in the table shown by fig1 . the fig1 graph demonstrates that the current occlusion device 100 a , as constructed , may exert only a very nominal pressure against the vessel wall which is insufficient to damage the intima or media of the blood vessel . to create an occlusion of the vessel , however , the force exerted against the wall location 212 should be greater than the systolic blood pressure or there may be an incomplete seal and leakage of blood around the device . the current device 100 a , because of the combination of structural features , can achieve an outward radial force greater than the patient &# 39 ; s systolic blood pressure by providing a minimal amount of inherent outward radial force insufficient to damage the vessel wall added to the patient &# 39 ; s transmitted systolic blood pressure and it can do so relatively independently of the diameter of a blood vessel , as demonstrated in the graph . hence , over a range of sizes , a consistent and balanced limited inherent outward radial pressure can be achieved . calculations reveal that a systolic blood pressure of 150 mm hg would demand at least 285 grams of outward radial pressure from a balloon or even the prior art funnel catheter to occlude a blood vessel . at this level , a segment of the arterial wall adjacent to the upstream balloon face may experience 570 grams of force as there would be at least 285 grams of outward radial force provided by the balloon and 285 grams from the 150 mm hg blood pressure . this may be enough to damage the vessel wall and create immediate or delayed complications . the occlusion devices of the present disclosure may subject the vessel wall to only 285 grams from the transmitted blood pressure ( which it is adapted to withstand ) and 1 . 4 grams from the inherent outward radial force of the devices . hence , the occlusion devices of the present disclosure may add only 0 . 5 % added pressure to the wall over the transmitted blood pressure whereas a balloon or even the prior art funnel catheter needs 100 % added pressure to occlude . hence , the occlusion devices of the present disclosure may be dramatic improvements in safety over prior art devices as vessel occlusion can be accomplished over a wide range of vessel sizes , flow rates and blood pressures by exerting a very minimal outward radial pressure on the vessel wall which is insufficient to damage to the vessel wall . by providing a membrane devoid section of braid 200 through which the blood may flow into the space between the inner shaft 196 of the device 100 a and the membrane containing braid 200 , the total force of the device will generally always exceed the patient &# 39 ; s systolic blood pressure . the systolic blood pressure will often be exceeded by the inherent outward radial force of the braid 200 ( which is less than one gram in many instances ) as the outward radial force of the braid 200 and the transmitted systolic blood pressure will often combine to press the membrane containing segment of the braid against the vessel wall preventing any leakage of blood around the device 100 a . to create a section of tubular braid 200 with portions that are impervious to flow and other portions in which fluid and blood may flow freely though , there may be several different methods available . dip coating is one very practical method to apply the elastomer to the braid 200 and the braid 200 may be dipped into a solution of the elastomer just enough to make part of the section of tubular braid 200 impervious to fluids leaving the non - dipped portion free of the elastomer . such dip coating can be somewhat inexact and tedious however . it may be appropriate to dip the entire section of tubular mesh braid 200 into the elastomer or coat the entire section in some other manner and then laser cut the elastomer from the intended porous portion of the braid 200 . this latter method can be more exact and precise and can leave a portion of the tubular braided section 200 with an elastomeric membrane or coating and part of the section with no elastomer and freely porous . there are other means known in the art of creating porous and non - porous sections of tubular braid . in some cases , it may be advantageous to provide another device to propel a blood clot or other substance into the mouth of a catheter or even to expand to serve as a filter or an additional occlusion device . this may include a device to engage the blood clot and pull it toward the catheter mouth or opening . prior art traction devices include balloon catheters , which are known to damage the vessel wall when fully expanded , and braided devices such as described in my prior u . s . pat . no . 6 , 635 , 068 , entitled “ occlusion , anchoring , tensioning and flow direction apparatus and methods for use .” even the latter prior art traction device may damage the vessel wall in at least some cases by a combination of the outward radial force and the irregular surface caused by the braid . a prior art traction device 300 is illustrated in fig1 comprising a tubular outer sleeve 302 coaxially containing or over an inner member or shaft 303 . an inner member 303 is attached to the distal end of the annular braid 304 at location 305 . the outer sleeve 302 is attached to the annular braid 304 at location 306 . fig1 shows the configuration in which the device 300 is inserted into the blood vessel bv . fig1 demonstrates the configuration utilized for the functioning of the traction device 300 , whether as a traction device on a thrombus or embolus , a filter device , or a tensioning device . the inner member 303 may be moved relative to the outer sleeve 302 as indicated by the arrow 307 . this relative motion can cause the annular braid 304 to expand radially as shown at location 308 . typically , the inner shaft of this device 300 is translated proximally relative to the outer shaft causing the braid to expand in a more or less linear relationship to the degree of translation . the materials and construction of the braid for this traction device 300 may be chosen to increase the degree of outward radial force to insure anchoring , tensioning , and occlusion and to maximize the outward radial force . as demonstrated in fig1 , the wall 310 of the blood vessel bv may be expanded by the expansion of the wire basket 304 in this case as the basket is secured to the wall . in fact , the object of the prior art device 300 is to provide enough outward radial pressure to the vessel wall 310 to firmly secure it to the vessel wall so that it may be used as a tensioning device to advance other devices coaxially over it , to occlude the vessel and to anchor it firmly to the vessel wall . in these instances and for these applications , it may be advantageous to create an expansile element that exerts excessive outward radial force to the vessel wall to achieve the desired results in that particular application . the vessel wall 310 may easily be damaged by the intended overexpansion or the inadvertent overexpansion of the braid , or other expansile element , in a vessel . this damage is illustrated in fig1 by the area of hemorrhage or dissection 311 in the media of the blood vessel wall 310 . this damage may incite the exuberant reparative effort of the blood vessel bv that results in restenosis . this damage caused by the uncontrolled expansion and distension of the blood vessel bv can stimulate a cascade of events in which smooth muscle cells and other pleuripotential cells migrate toward the lumen and create a scar of sort that may occlude or severely narrow the vessel demanding further intervention at a later date . addressing this dilemma is an object of the present disclosure . the current inventor has conducted experiments have shown that damage to the arterial wall can be avoided by such a device if constructed of nitinol wires treated to provide a combination of stiffness and flexibility that not only creates a limited amount of outward radial force against the wall , but also causes the braid to elongate when placed in smaller vessels . this limited radial force and elongation are illustrated by the present traction device 100 a in fig1 . when the inner member 303 is retracted relative to the outer sleeve 302 , the braid or other expansile element 304 expands to the vessel wall 310 but does not expand the wall 310 . instead , because of the combination of structural features , the braid or other expansile element 304 elongates and does not distend or damage the vessel wall as in fig1 . there is no hemorrhage or dissection 311 with the elongation in fig1 as there is with the forceful radial expansion illustrated in fig1 . this lack of hemorrhage or dissection 311 may prevent the restenosis reaction from occurring . generally , the traction device 300 a may not anchor or serve as a tensioning means as in the prior art device 300 , but the device of fig1 may still function as a filter , clot traction device , or occluder . it is important that the improved current device provide a consistent and balanced outward radial force over a fairly wide range of vessel diameters as well . in other words , the current device , because of a combination of structural elements , should provide a limited amount of outward radial force insufficient to damage the vessel wall which is independent of the vessel wall diameter over a range of vessel diameters . while the current disclosure discusses the specific location of the elastomer and the elastomer free portion of the braid , there may in certain instances be a need for the elastomer to cover or be applied to only a minimal section of the braid . this may especially be true when complete occlusion is not desirable . in these instances , the devices may be constructed similarly to the above examples , with the elastomer free section comprising a majority or even all of the braid . the elastomer containing section may be small or absent in at least these cases . the elastomer containing section may be placed on the braid so that a portion of the funnel is impermeable , but the funnel apparatus would typically not obstruct or occlude flow . the traction device 300 a of the present disclosure may utilize 0 . 004 ″ diameter nitinol wires that have been heat treated to provide a combination of stiffness and flexibility and by varying the pics per inch , the number of wires , the shape of the wires , the crossing angle of the wires as well as the density of any elastomeric coating , if any , so that the expanded device will achieve a “ programmed ” outward radial force even if attempts are made to expand the device beyond the diameter of the vessel . as the graph in fig1 demonstrates , a braid section fully expanded to 5 . 5 mm in a 5 . 5 mm vessel can create about 12 grams of outward radial force or compressive unloading . it can essentially create the same amount of outward radial force when expanded with the same degree of translation of the inner shaft relative to the outer shaft over a range of different sized vessels because the braid section elongates rather than expands outward as a result of the properties inherent in the nitinol wires and the braid pattern . the linear relationship of the length of translation of the inner wire to the outer sleeve with the degree and outward force of expansion present in prior art devices can be overcome in the present traction device by the use a combination of the flexibility of the nitinol wires which is a result of size of wires and material choice , by heat treating , the pics per inch , the number of wires in the braid , the crossing angle of the braid , the relative stiffness of the silicone or other elastomer amongst other items . particularly , heat treating the nitinol wires in a jammed state where the braid is compressed into the smallest diameter and elongated will generally cause the braid to display a minimal amount of outward radial force independent of the vessel size . smaller and more flexible wires will also tend to cause the device to elongate rather than expand outward . utilizing a small braid angle can be another important structural component to facilitate elongation vs . outward expansion and may be as important as other structural features . with a larger braid angle , where one wire crosses another , that approaches 90 degrees , the braid can resist collapsing and can maintain a relatively large amount of outward radial force . it can also resist elongation , which may be part of the collapsing process . with smaller braid angles , the tubular braid may not possess as much radial strength or outward radial force as the braid wires can tend to move relative to each other to even smaller angles resulting in elongation of the tubular braid . this elongation can be very important as it may prevent excessive outward radial force from being transmitted to the vessel wall and potentially damaging the wall . this improvement over the prior art traction devices ( e . g ., traction device 300 ) utilizing a combination of the structural features above can prevent damage to the vessel wall by providing an effective way to pull clot or other substance into a catheter , whether a standard catheter or a braided funnel catheter described herein . it may also be utilized in other non - balloon expansile devices as mentioned above . for example , if the prior art traction device 300 were placed in a 5 . 5 mm diameter vessel and expanded to 5 . 5 mm so that it abuts the wall , it would provide a certain amount of outward radial force against the wall . if the same device were utilized in a 3 . 5 mm vessel and expanded to 5 . 5 mm diameter , the prior art traction device 300 may over - distend the wall of the vessel 2 mm or so to the 5 . 5 mm diameter creating a situation that may very easily cause damage to the vessel wall as previously illustrated in fig1 which may result in restenosis and other negative events . overexpansion such as in this example may be common as the prior art traction devices can be so delicate that they cannot be easily visualized by fluoroscopy during a procedure , so the operator expands the braid by “ feel ” which is inexact at best . instead of under expanding the prior art traction device and being ineffective , the tendency may be to over expand it . an alternative to prevent this overexpansion and subsequent damage to the vessel wall is to size the expansile device to the size of the vessel and utilize a specifically sized device for each vessel treated . for a 5 . 5 mm vessel , one may use a device sized to provide a relatively low amount of outward radial force , and for a 3 . 5 mm diameter vessel , one may use another device sized to provide a relatively low amount of outward radial force to the vessel wall of that particular size in that case . this custom sizing can be effective in limiting the damage to the vessel wall , but can create stocking and inventory problems and may drive the cost of utilizing these devices upward as a facility must stock multiple different sized devices to cover the range of vessel sizes from 2 mm or so in the cerebral , coronary , and below the knee arterial circulation to 8 - 10 mm in the iliac artery to 16 mm in the iliac veins and even larger in the inferior vena cava and all sizes in between . moreover , it may frequently be necessary to utilize the same type of device at different locations within the same patient , which may create the need for a catheter or device exchange which is time consuming and involves utilizing a new device for the second location which may cost thousands of dollars . in essence , the use of specifically sized devices that avoid damage to the vessel wall may demand the costly and time consuming use of two or more specifically sized devices in different vessels in the same patient rather than the serial use of one device which may safely and more time efficiently treat a wide range of sizes . hence , there is a real need to control the outward radial pressure exerted on the vessel wall in expansile devices to prevent vessel wall damage such as this traction device , and also in embolic protection filters , occlusion devices , other traction devices as well as most any expansile device by “ programming ” the expansile force into the device to create as little outward radial force as possible over a wide range of diameters . an elastomer may be provided to cover all or part of the braid 304 , especially if the present traction device 300 a is used as a vascular occluder , and may increase or decrease the outward radial force depending on the properties , thickness and consistency of the elastomer . a braid 304 of different programmed properties may be utilized in that instance . yet another way of controlling the outward radial force may be to utilize an elastic or elastomeric material , such as , but not limited to , silicone , urethane , neoprene , isoprene , pebex , chronoprene and the like for the inner member or outer sleeve , so that the inner member stretches or the outer member compresses if attempts are made to over expand the device within a vessel . instead of the excessive outward radial force being transmitted to the wall , in this case , it can be transmitted to the at least somewhat elastic inner member by stretching said member after a selected outward radial pressure is achieved by the braid or expansile component or by compressing the outer sleeve after a selected outward radial pressure is achieved by the braid or expansile component , or by utilizing both . as well , ways to elongate the braid may also be utilized with either ways to stretch the inner member and with ways to compress the outer sleeve , or both , to prevent outward radial force from being transmitted to the vessel wall beyond a selected level . furthermore , since the outward radial force is usually created in a linear relationship by pulling the inner member in relation to the outer sleeve , a spring in the handle of the device attached to the inner member may prevent the full expansion of the braid and limit the outward radial pressure . hence , a spring may be used alone or in combination with any or all of the features listed above to limit the outward radial pressure . yet another way of providing minimal outward radial force to the vessel wall 310 with an expandable braid device 304 , as illustrated in fig1 , is to provide an impermeable or partially impermeable elastomer or membrane 315 on at least the distal section of the braid 304 and an elastomer or membrane free section 316 proximally so that the patient &# 39 ; s blood pressure may be transmitted beneath the impermeable or partially impermeable aspect of the braid 315 as shown by arrows 317 . the transmitted blood pressure may enhance the expansion of the expandable basket 304 against the vessel wall 310 . hence , as in the apparatus 300 b illustrated in fig1 , most of the outward radial force of the expandable basket 304 to the wall of the blood vessel 310 may be from the patient &# 39 ; s own blood pressure and not from the inherent outward radial force of the expandable braid 304 . in essence , the membrane or elastomer 315 may preferably be combined with either one or more of the previously discussed structural features of the braid to accomplish this version . this combination of structural features including the features that cause the braid to lengthen rather than expand and the membrane 315 may minimize the chance of damage to the blood vessel 310 by excessive outward radial force as is present in prior art devices . referring back to fig3 and 4 , a dilator or obturator 220 may be used in conjunction with the funnel catheter or occlusion device 100 a . since in the contracted configuration , the braid 200 is on the outside of the inner sleeve 196 and exposed to the vessel wall 210 , there can be the potential for the braid 200 to engage the vessel wall 210 and damage the intima as the braid 200 may not be as smooth as a usual smooth catheter exterior . the leading edge of the braid 200 at the tip of the catheter may particularly have a lower smoothness . hence , it may be advantageous to provide a way to create a smoother leading edge of the catheter . usually , an obturator or inner catheter 220 can be utilized coaxially within the catheter and over the guide wire to provide a more or less smooth transition from the guide wire ( 0 . 014 ″ to 0 . 035 ″) to the catheter shaft ( 0 . 044 ″ to 0 . 069 ″). in standard catheters , this configuration of guide wire , obturator or inner catheter 220 , and then the catheter may be adequate but with the leading edge of the current catheter comprising a section of braid and two wall thicknesses because of the inner and outer sleeves , there still may be some exposed braid over the obturator or inner catheter which may engage the vessel wall . to create a smooth transition and protect the wall from damage or an abrasion of the intima by the exposed braid , the obturator or dilator 220 may be adapted as shown in fig4 to fill the 0 . 006 ″- 0 . 010 ″ difference between the od of the contracted funnel catheter and then od of the obturator or inner catheter . fig5 shows that the dilator or obturator 220 may be sized so that it fits within the inner diameter of the funnel catheters 100 and 100 a previously described , but with an oversized tip or distal end that extends beyond the distal end of the funnel catheter when the funnel catheter is in a contracted or tubular configuration . since the distal tip 221 of the dilator 220 should be just as large as the outer diameter ( od ) of the funnel catheter 100 , 100 a and oversized relative to the inner diameter ( id ) of the funnel catheter 100 , 100 a , it should be compressible to insert it through the hub end of the funnel catheter 100 , 100 a and to remove it from the funnel catheter 100 , 100 a once the funnel catheter 100 , 100 a is in place at a target location in the vasculature . to accomplish this , the dilator 220 can have novel features that can provide for protection against injury to the arterial wall by the braided section and allow the oversized tip 221 to be inserted and withdrawn through the funnel catheter even though the id of the funnel catheter is smaller than the od of the tip of the dilator . the shaft 222 of the dilator 220 may be sized to fit within the id of the funnel catheter inner sleeve 196 . the tip 221 of the dilator 220 may be the same size as the od of the funnel catheter 100 , 100 a . the dilator 220 comprises a lumen 223 for receiving a guide wire . so that the tip of the dilator 220 may fit through the id of the funnel catheter 100 , 100 a , it must be compressible . one way of providing compressibility may be to utilize a softer durometer substance within the tip . another way may be to place a notch or a wedge shaped cutout 230 in the tip as demonstrated in fig6 which is a cross section of fig5 at a location a . still another way may be to enlarge the guide wire lumen 223 to accommodate the compression needed for the larger tip to fit into the smaller lumen or to connect the guide wire lumen 223 to the notch 230 as demonstrated in fig7 . utilizing one or more of these ways can allow the larger tip 221 to compress so that it may be inserted and removed through the smaller catheter lumen . placing the obturator device 220 through the hub or proximal end of the catheter 100 , 100 a should not be problematic as means to compress the tip 221 outside the body are readily available and may comprise just ones finger and thumb or a special tool to receive the dilator tip and compress it to a smaller size by advancing it into a rigid funnel like structure . when placed through the catheter lumen as demonstrated in fig8 , the oversized tip 221 of the dilator 220 may cover the leading edge of the funnel catheter tip 206 and prevent any injury to the vessel wall that may be cause by the exposed braid otherwise . by angling the lumen 223 toward the notch 230 at the end of the dilator 220 , the guide wire can be subtlety directed over that notch 230 and toward the wall of the vessel that one does not want the gap to encounter , hence “ protecting ” the gap or partially covering it and directing that portion of the tip away from the vessel wall . removing the oversized tip can be facilitated by deploying the funnel apparatus of the funnel catheter as illustrated in fig9 initially and then retracting the oversized , but compressible , dilator tip into the catheter shaft . while the primary objective of the oversized tip of the dilator 220 may be to protect the vessel wall from the catheter tip , the oversized tip 221 may also be utilized to retract thrombus or other material into the catheter . if utilized in a standard catheter , for example , the oversized but compressible dilator tip 221 and dilator 220 may be removed by simply retracting it into and out of the catheter shaft . while preferred embodiments of the present invention have been shown and described herein , it will be obvious to those skilled in the art that such embodiments are provided by way of example only . numerous variations , changes , and substitutions will now occur to those skilled in the art without departing from the invention . it should be understood that various alternatives to the embodiments of the invention described herein may be employed in practicing the invention . it is intended that the following claims define the scope of the invention and that methods and structures within the scope of these claims and their equivalents be covered thereby .
an occlusion apparatus comprises inner and outer sheaths and an expandable flexible tubular sleeve . the occlusion apparatus is advanced to a target site in the blood vessel . a dilator having a soft , compressible tip may be advanced through a lumen of the inner sheath to facilitate the advancement of the occlusion apparatus . the sheaths are translated relative to one another to expand the flexible tubular sleeve to a funnel shape with a distal flush portion contacting the blood vessel inner wall and a proximal tapered portion . the proximal portion is fluid permeable so that blood can pass through to apply pressure on the vessel wall through the distal portion . a capture or traction device can be advanced out of the inner sheath lumen and retracted back therein to capture thrombus . the distal portion of the device may comprise an expandable mesh braid with a memory characteristic to limit expansion .