The present invention relates to aspiration systems used in phacoemulsification procedures, and more particularly, to aspirations systems employing small bore elements to improve operation.
Typical surgical instruments suitable for phacoemulsification procedures on cataractous lenses include an ultrasonically driven phacoemulsification hand piece with a cutting needle and an irrigation sleeve, and a control console. The hand piece is attached to the control console by an electric cable and flexible tubing. The flexible tubing supplies irrigation fluid to the surgical site and carries aspiration fluid from the surgical site to a waste or discard reservoir.
During a phacoemulsification procedure, the tip of the cutting needle and the end of the irrigation sleeve are inserted into the anterior segment of the eye through a small incision in the eye's outer tissue. The surgeon brings the tip of the cutting needle into contact with the lens of the eye, so that the vibrating tip fragments the lens. The resulting fragments are aspirated out of the eye through the interior bore of the cutting needle, along with irrigation fluid provided to the eye during the procedure.
Throughout the procedure, irrigating fluid is infused into the eye, passing between the irrigation sleeve and the cutting needle and exiting into the eye at the tip of the irrigation sleeve and/or from one or more ports or openings formed into the irrigation sleeve near its end. This irrigating fluid prevents the collapse of the eye during the removal of the emulsified lens, protects the eye tissue from the heat generated by the vibrating of the ultrasonic cutting needle, and suspends the fragments of the emulsified lens for aspiration from the eye.
During the surgical procedure, the console controls irrigation flow rates and aspiration flow rates to maintain a proper intra-ocular chamber balance in an effort to maintain a relatively consistent fluid pressure at the surgical site in the eye.
Aspiration flow rates of fluid from the eye are typically regulated by an aspiration pump that creates a vacuum in the aspiration line. The aspiration flow and/or vacuum are set to achieve the desired working effect for the lens removal. While a consistent fluid pressure in the eye is desirable during the phacoemulsification procedure, common occurrences or complications create fluctuations or abrupt changes in fluid flow and pressure at the eye. One known cause for these is occlusions or flow obstructions that block the needle tip. This common, and sometimes desirable occurrence, results in a sharp increase in vacuum in the aspirating line. When the occlusion is removed, the resulting high demand for fluid from the eye to relieve the vacuum can cause a sudden shallowing of the anterior chamber, as the aspiration flow momentarily sharply increases over the irrigation flow.
The degree of shallowing in the eye is a function of vacuum level within the aspiration path when the occlusion breaks, as well as resistive and compliance characteristics of the fluid path. Increased resistance in the aspiration path reduces the flow rate associated with occlusion break and thereby lessens the pressure drop from the irrigating source to the eye and the resulting shallowing of the anterior chamber.
The problem of occlusion surge has been addressed in the past in a number of ways. One method includes adding a reduced cross-sectional orifice to create a barrier reducing flow. While such a reduced area reduces the effects of occlusion surge, reduction of aspiration path cross-section can also increase the potential for clogging during the procedure. Other methods have been used or proposed that involve torturous paths, with corners, angles, and fluid restrictors that are also subject to clogging. Some prior solutions involve a resistive element at or near the pump. However, the effectiveness of these solutions is limited due to the relatively large tubing compliance between the resistive element and the eye. Another attempted solution has been the use of increased lengths of flexible aspiration tubing in an attempt to increase overall tubing resistance. This solution of adding flexible tubing length has the undesirable effect of adding additional compliance to the aspiration path. The additional compliance increases the demand for fluid from the eye during occlusion break, sometimes entirely offsetting the benefits obtained by the longer tubing length.
Methods with small bore aspiration lines, such as lines with a diameter of 0.050 inches or less, have generally been avoided because small bore lines may become easily clogged, potentially creating inconsistent flow rates, resulting in high levels of occlusion surge, and possibly resulting in undesirable levels of trauma during the surgical procedure. In addition, methods with small bore aspiration lines have generally been avoided because, as a result of the small bore with increased wall resistance, pumping that achieves a desirable flow rate can be difficult.
In one exemplary aspect, the present disclosure is directed to an assembly for a phacoemulsification surgical system. The assembly includes a phacoemulsification hand piece configured to deliver irrigating fluid to a surgical site. The phacoemulsification hand piece includes an ultrasonic tip having a lumen sized and configured to aspirate aspirating fluid from the surgical site. The assembly also includes an irrigation system arranged to provide the irrigating fluid to the phacoemulsification hand piece to irrigate the surgical site and includes an aspiration system arranged to aspirate the aspirating fluid from the surgical site. The aspiration system includes an aspiration path within the phacoemulsification hand piece. The aspiration path extends from the ultrasonic tip and is arranged and configured to permit flow of the aspirating fluid through the hand piece. The aspiration system also includes a flexible small bore aspiration tubing in fluid communication with the aspiration path. The small bore aspiration tubing has a nominal inner diameter smaller than about 0.050 inch (other diameters are also contemplated) to reduce levels of occlusion surge within the surgical system. The inner diameter is substantially consistent through the length of the small bore aspiration tubing. A high-output, peristaltic pump communicates with the small bore aspiration tubing and is operable to create a flow of about 60 cc/min. through the small bore aspiration tubing.
In some aspects, the small bore aspiration tubing includes a flared portion on the inner diameter of at least one end, wherein when in an unloaded condition, the flared portion has an inner diameter larger than the nominal inner diameter of the small bore aspiration tubing. In additional aspects, the assembly includes a connector configured to receive at least a portion of the flared portion of the small bore aspiration tubing. The connector may be sized to apply radial compression on the flared portion when the flared portion is inserted in the connector such that when the small bore aspiration tubing is disposed within the connector, the inner diameter of the flared portion is about the same diameter as the neck and the nominal diameter of the small bore aspiration tubing.
In another exemplary aspect, the present disclosure is directed to a small bore aspiration system arranged to receive aspiration fluid from an ultrasonic tip used in a phacoemulsification surgical assembly. The system includes an aspiration path within the phacoemulsification hand piece that extends from the ultrasonic tip and is arranged and configured to permit flow of the aspirating fluid through the hand piece. It also includes a flexible small bore aspiration tubing in fluid communication with the aspiration path. The small bore aspiration tubing has a nominal inner diameter smaller than about 0.050 inch (other diameters are also contemplated) to reduce levels of occlusion surge within the surgical system, and the inner diameter being substantially consistent through the length of the small bore aspiration tubing. The system also includes a high-output, peristaltic pump in communication with the small bore aspiration tubing.
In yet another exemplary aspect, the present disclosure is directed to a method for aspirating a surgical site with an aspiration system of a phacoemulsification surgical system. The method includes the steps of creating a vacuum in an aspiration system of a phacoemulsification system, directing fluid through a needle of the phacoemulsification hand piece, and directing fluid through an aspiration passage within the hand piece having a size ratio between the aspiration passage bore inner diameter and the needle bore inner diameter of less than about 1.5 (or, for example, 1.3). The method also includes directing fluid through a small bore flexible aspiration tubing extending from the hand piece to a fluid cassette. The small bore flexible aspiration tubing has a substantially consistent nominal diameter across its length that is less than about 0.050 inch (other diameters are also contemplated). In some embodiments, the size ratio between the small bore flexible aspiration tubing inner diameter and the needle bore inner diameter is less than about 1.5 (or, for example, 1.3). The method also includes directing fluid into a cassette and a pump configured to create a vacuum in the aspiration system.
It is to be understood that both the foregoing general description and the following detailed description are exemplary and explanatory only and are intended to provide further explanation of the invention as claimed. The following description, as well as the practice of the invention, sets forth and suggests additional advantages and purposes of the invention.
The accompanying drawings, which are incorporated in and constitute a part of this specification, illustrate several embodiments.
Reference is now made in detail to several exemplary embodiments, examples of which are illustrated in the accompanying drawings. Wherever possible, the same reference numbers are used throughout the drawings to refer to the same or like parts.
This disclosure is directed to an aspiration system that may achieve lower levels of occlusion surge than currently known systems under similar conditions. These lower levels derive from a novel, small bore aspiration line that provides increased fluid resistance when compared to known systems. This increased fluid resistance dampens or reduces the levels of occlusion surge in the aspiration line, potentially resulting in more stable and predictable surgical processes.
The small bore aspiration tubing decreases occlusion surge levels in at least two ways. First, the smaller diameter of the small bore fluid path introduces a greater level of wall resistance than larger bore fluid paths. This wall resistance decreases the amount of flow variation over short periods of time, rendering the flow more consistent, with lower levels and more controlled surge when surges occur. Second, the small bore aspiration tubing, due to its smaller surface area than larger bore aspiration tubes, is subject to less compliant deformation (radial collapse) as a result of high vacuum levels within the tube, as may occur when aspiration flow is limited or blocked by an occlusion.
As indicated above, however, small bore aspiration tubing has generally been considered easily clogged. Therefore, small bore aspiration tubing having a diameter of less than about 0.050 inch have not typically been used in aspiration lines. However, the small bore aspiration tubing disclosed herein may achieve suitable, consistent flow rates with reduced clogging by using consistent-flow junction components and suitable relative dimensions between components. Thus, small bore aspiration tubing can be used, with acceptable flow tendencies, to decrease the level of occlusion surges and provide more control during surgical procedures.
The irrigation system 300 extends between the sterile solution reservoir 304 and the hand piece 118, and carries fluid to the surgical site (labeled in
In some embodiments, the aspiration system 302 includes an aspiration path 316 in the hand piece 118, a small bore flexible aspiration tubing 318, a pressure sensor 320, a pump 322, a vent valve 324, a drain line reservoir 326, and a drain reservoir 328. A hand piece connector 330 connects the aspiration path 316 in the hand piece 118 to the small bore flexible aspiration tubing 318. A cassette connector 332 connects the flexible aspiration tubing 318 to the cassette aspiration line in the cassette 314. As can be seen, the aspiration system 302 extends from the surgical site (eye) to the drain reservoir 328. It carries away fluid used to flush the eye as well as any emulsified particles. As described above with reference to the flexible irrigation tubing 308, at least a portion of the small bore flexible aspiration tubing 318 may be formed of the flexible tubing 112. In some embodiments, the aspiration system 302 is formed of multiple segments, with some segments being rigid and others being flexible. Also, in some embodiments, at least a portion of the aspiration system 302 is formed in the cassette 314 that cooperates with the console 100 in
For ease of explanation, the flexible tubing 112 will be described first, followed by a description of additional components of the aspiration system 302.
The flexible tubing 112 extends from a proximal end 400 configured to connect to the cassette 314 to a distal end 402 configured to connect to the hand piece 118 through the hand piece connector 330. In this embodiment, the irrigation and aspiration flexible tubings 308, 318 are connected at the distal end 402, forming a dual lumen distal end. This facilitates connection to the hand piece 118, simplifying assembly of the surgical components prior to a surgery. In other embodiments however, the irrigation and aspiration tubing 308, 318 are independent tubes entirely, and in yet other embodiments, the irrigation and aspiration tubing 308, 318 are entirely connected as dual lumen systems. Other arrangements are contemplated, including arrangements where the flexible tubing 112 is formed as dual lumen system between the distal and proximal ends, but the proximal and distal ends are each split into two independent lines.
As is apparent in
The inner diameter of the small bore aspiration flexible tubing 318 is about 0.050 inches or less (other diameters are also contemplated). In the example shown, the small bore flexible tubing 318 has an average inner diameter in the range of about 0.040-0.050 inch, and in some embodiments, about 0.045 inch (other diameters are also contemplated). Accordingly, the inner diameter is about 27% ((0.062−0.045 inch)/0.062 inch) smaller than the aspiration tubes used in some conventional systems. In other examples, the average inner diameter is in the range of 0.035-0.045 inch (other diameters are also contemplated). The inner diameter is substantially consistent across the axial length of the aspiration flexible tubing 318, without orifices or bottle-necks that would increase the tubing resistance. Further, the walls are substantially smooth, such that the flow through the tubing is substantially laminar, without disrupting barriers.
The inner diameter of the aspiration flexible tubing 318 may be considerably smaller than the inner diameter of conventional aspiration tubes used in phacoemulsification systems. Because of the challenges surrounding the use of smaller aspiration tubing, conventional systems use tubing with an inner diameter within the range of, for example, about 0.060 or larger, typically about 0.062 inches. Here however, small bore tubing, that is, tubing with an inner diameter of about 0.050 inch or less, is used to control the levels of occlusion surge to a degree that may not be obtainable using the conventional flexible larger tubing.
The smaller diameter of the small bore aspiration tubing 318 provides a higher tube resistance than that of aspiration systems using larger diameter aspiration lines. As discussed above, this higher tube resistance decreases the levels of occlusion surge occurring when the tip 334 becomes occluded during a surgical procedure, providing more control to a surgeon. In addition, because the small bore aspiration flexible tubing 318 has a smaller surface area on the inner diameter, and has substantially the same outer diameter as the irrigation line, the small bore aspiration flexible tubing 318 may be less compliant to radial compression from vacuum surges than larger bore aspiration tubes. This reduced compliance may result in smaller levels of occlusion surge as explained above.
The aspiration system 302 is also configured to reduce the propensity for clogging at the junction of the small bore aspiration flexible tubing 318 and the aspiration path 316 and at the junction of the small bore aspiration flexible tubing 318 and the cassette 314. In some embodiments, it does this by cooperating with the connectors 330, 332 to provide a smooth transition from the hand piece 118 and to the cassette 314. For example, the small bore aspiration flexible tubing 318 has a flared inner diameter at the regions of the distal end 402 and the proximal end 400. For ease of discussion, this flared inner diameter will be discussed only with reference to a proximal end portion 404 at the small bore tubing's proximal end 400. It is understood that the distal end 402 may include the same or similar structure. This proximal end portion 404 will be described with reference to
Turning to
The aspiration fluid path 316 (
As can be seen in
In some embodiments, the second bore 406 includes an open receiving bore end 420, an inner bore surface 422, and a bell-shaped curving bore surface 424 leading to the neck 416. The second bore 406 is sized to receive an end of the aspiration path 316 through the hand piece 118. Accordingly, the bore 406 has a diameter sized to receive the end of the aspiration path 316.
Since in some embodiments, the aspiration path 316 is sized in the range of about 0.062 inch or larger, the flow from the aspiration path 316 is funneled as a nozzle into the neck 416. The bore 406 is particularly shaped with the bell-shaped curve to avoid clogging, while still carrying the fluid and emulsified particles through the neck 416. Accordingly, to minimize the propensity for clogging, the length of the bore 406 at its largest diameter is minimized to facilitate particles remaining oriented along the flow lines. In addition, instead of having a stepped or squared end as conventional connectors do, the connector 330 has a bell-shaped, curved surface 424 that provides an uninterrupted smooth transition from a larger diameter of the bore end 420 down to the diameter of the neck 416, which, as explained above, substantially matches the nominal diameter n of the small bore aspiration tubing 318. The bell-shape helps by narrowing the length required for the transition from the large diameter to the neck while still providing a smooth flow path. This may provide a better flow than a long linearly tapering path. Thus, the tubing connector 330 helps the small bore aspiration system operate effectively to control occlusion surge.
The second end 448 of the connector 332 is configured to interface with the cassette 314. In the embodiment shown, the cassette 314 is a conventional cassette and includes a fluid pathway connectable with the connector 332. The pathway 332 has an inner diameter sized greater than the inner diameter of the small bore aspiration tubing 318. Accordingly, the connector 332 is particularly configured to receive the fluid passage from the cassette 314. The second end includes an open receiving end 440, a conical surface 442, and a bore end 444 leading to the neck 416a.
Because the connector 332 is particularly designed to receive the aspiration tubing end, and deform the end portion in a manner not overly restricting flow, the propensity for clogs is reduced, resulting in a smoother, more laminar transition through the connector than conventional aspiration systems. This helps make the use of a small bore aspiration tubing to control occlusion surge more effective, without the drawbacks of clogging. Further, as described above, the taper on the outer diameter of the small bore aspiration tubing 318 discussed with reference to
The pump 322 of the aspiration system 302 is associated with the cassette 314 and is configured to create a vacuum in the aspiration system 302 to draw fluid and emulsified particles from the surgical site. The high fluid resistance associated with the small bore aspiration tubing 118 may result in greatly reduced efficiency for most peristaltic pumps. This fluid resistance, while beneficial for reducing the levels of occlusion surge, can also result in the inability to generate desire levels of aspiration flow rate (typically up to 60 cc/min) or can require a need to run the pump at a very high rate of speed resulting in objectionable acoustic noise. Accordingly, because of the small bore of the aspiration tubing 318, a conventional pump may not achieve the vacuum required for suitable flow at the surgical tip. The pump 322, therefore, may be a high-output pump capable of creating the vacuum necessary to achieve suitable flow rates through the small bore aspiration tubing 318. In some examples, the pump 322 is a bidirectional peristaltic pump. In some embodiments, the pump 322 represents multiple pumps that operate in parallel. In some aspects, the pump is as described in U.S. patent application Ser. No. 12/755,539, filed Apr. 7, 2010, which is incorporated herein by reference.
Accordingly, the aspiration system 302 employs small bore aspiration lines, with a diameter of 0.050 inches or less (other diameters are also contemplated) to achieve lower levels of occlusion surge than currently known systems under similar conditions. In some embodiments, the small bore aspiration tubing 318 inner diameter is within the range of 0.040-0.050, and in some examples, around a nominal diameter of about 0.045 inch. In other examples, the average inner diameter is in the range of 0.035-0.045 inch (other diameters are also contemplated).
The small bore lines provide increased fluid resistance that dampens or reduces the levels of occlusion surge in the aspiration line. These lines accomplish this by introducing a greater level of wall resistance than larger bore fluid paths and by being less compliant when subjected to high vacuum levels within the tubing. At the same time, the aspiration system maintains suitable flow rates with reduced clogging. This decreases the level of occlusion surges and provides more control during surgical procedures.
In one embodiment of the aspiration system 302, the aspiration fluid path 316 in the hand piece 118 has a small bore inner diameter, less than about 0.050 inches (other diameters are also contemplated), and in some embodiments, matching one or both of the inner diameter of the small bore aspiration tubing 318 and the inner diameter of the ultrasonic tip 334.
Aspiration fluid paths within a conventional hand piece are larger bore tubes having an inner diameter typically sized greater than 0.060 inches. This may be considerably larger than a conventional lumen size of the ultrasonic tip (typically 0.045 inches or less). As such, in conventional systems, emulsified particles passing through the tip may have a non-symmetrical shape and may be oriented longitudinally to the direction of flow. As the particles pass from the tip into the aspiration path in a conventional hand piece, the particles have an opportunity to reorient. These reoriented particles have a greater propensity to clog the aspiration system further down line.
In this embodiment, however, the aspiration fluid path 316 has a small bore inner diameter, less than about 0.050 inches, sized to cooperate with the lumen diameter of the ultrasonic tip and the small bore aspiration tubing 318. In some embodiments, the inner diameter of the aspiration fluid path 316 is within the range of 0.040-0.050, and in some examples, around a nominal diameter of about 0.045 inch. In other examples, the average inner diameter is in the range of 0.035-0.045 inch (other diameters are also contemplated). In other embodiments, the aspiration fluid path 316 lumen is sized to match that of the ultrasonic tip lumen (i.e., the needle bore).
In some embodiments, the size ratio between the inner diameter of the small bore aspiration tubing 318 and the inner diameter of the ultrasonic tip may be minimized. For example, a size ratio between the aspiration tubing 318 inner diameter and the needle bore inner diameter may be less than about 1.3. In one embodiment, the needle bore inner diameter may be approximately 0.0354 inches and the aspiration tubing 318 inner diameter may be approximately 0.045 inches for a size ratio between the aspiration tubing 318 inner diameter and the needle bore inner diameter of about 1.27 (i.e., 0.045 inches/0.0354 inches). Other size ratios are also contemplated (e.g., 1.5).
Because its inner diameter size may be less than that of conventional systems, the aspiration path 316 in the aspiration system 302 creates a higher tube resistance. As discussed above, this higher tube resistance decreases the levels of occlusion surge occurring when the tip 334 becomes occluded during a surgical procedure.
In some embodiments, the inner diameter of the small bore aspiration tubing 318 may substantially match the inner diameter of the aspiration fluid path 316 in the hand piece. For example, a size ratio between the hand piece aspiration fluid path inner diameter and the needle bore inner diameter may also be about 1.3 (other size ratios are also contemplated). If the inner diameter of the aspiration fluid path 316 of the hand piece is the same as or less than that of the flexible aspiration tubing 318, then propensity for clogging can be further reduced. In this way, particles aligned longitudinally with the pathway stay longitudinally aligned, with less opportunity to reorient in a position that may result in clogging or occlusion of the aspiration system 302. In such embodiments, the tapering that occurs in the connector 330 may be replaced with a flat end that abuts the end of the aspiration path 316 and has a neck with a diameter substantially matching the nominal diameter of the aspiration path 316 and the small bore aspiration tubing 318.
In use, the flexible tubing 112 is attached to the hand piece 118 prior to conducting the surgery. Irrigation fluid is directed to the surgical site through the irrigation system 300. The aspiration system 302 conveys fluid from the surgical site to the waste reservoir or drain 328. This is accomplished by vacuuming fluid and emulsified tissue from the surgical site with the phacoemulsification needle tip 334. The fluid passes to the aspiration path 316 in the hand piece 118. The fluid then flows through the connector 330 into the small bore flexible aspiration tubing 318. The connector 330 is configured to minimize clogging by creating minimal turbulence and by minimizing transitions from diameters larger than the diameter of the small bore flexible aspiration tubing 318. The fluid flows though the small bore flexible aspiration tubing 318 to the cassette 314, and through the connector 332 at the cassette. As described above, the diameter of the inner flexible tubing is substantially maintained at its nominal size, even through the female connector 334 due to its flared configuration. The flow continues to the pump 322, which may be a high-output, bidirectional peristaltic pump.
Other embodiments of the invention will be apparent to those skilled in the art from consideration of the specification and practice of the invention disclosed herein. It is intended that the specification and examples be considered as exemplary only, with a true scope and spirit of the invention being indicated by the following claims.
This application claims the benefit of priority of U.S. Provisional Patent Application Ser. No. 61/423,752 titled “Small Bore Aspiration System”, filed on Dec. 16, 2010, whose inventors are Gary P. Sorensen and Eric Lee.
Number | Name | Date | Kind |
---|---|---|---|
2295840 | Grint | Sep 1942 | A |
3589363 | Banko | Jun 1971 | A |
3884238 | O'Malley et al. | May 1975 | A |
4019514 | Banko et al. | Apr 1977 | A |
4031896 | Ronnmark | Jun 1977 | A |
4117843 | Banko et al. | Oct 1978 | A |
4324243 | Helfgott et al. | Apr 1982 | A |
4418944 | Haines et al. | Dec 1983 | A |
4921477 | Davis | May 1990 | A |
4935005 | Haines | Jun 1990 | A |
5041096 | Beauchat et al. | Aug 1991 | A |
5364342 | Beauchat et al. | Nov 1994 | A |
5437678 | Sorensen | Aug 1995 | A |
5499969 | Beauchat et al. | Mar 1996 | A |
5585011 | Saaski et al. | Dec 1996 | A |
5651783 | Reynard | Jul 1997 | A |
5928203 | Davey et al. | Jul 1999 | A |
6059544 | Jung | May 2000 | A |
6149633 | Maaskamp | Nov 2000 | A |
6261283 | Morgan et al. | Jul 2001 | B1 |
6273878 | Muni | Aug 2001 | B1 |
6273894 | Dykes | Aug 2001 | B1 |
6293926 | Sorensen | Sep 2001 | B1 |
6402206 | Simmons et al. | Jun 2002 | B1 |
6436077 | Davey et al. | Aug 2002 | B1 |
6478781 | Urich et al. | Nov 2002 | B1 |
6572349 | Sorensen et al. | Jun 2003 | B2 |
6601879 | Donoho et al. | Aug 2003 | B2 |
6632214 | Morgan et al. | Oct 2003 | B2 |
6719011 | Cull et al. | Apr 2004 | B2 |
6740074 | Morgan et al. | May 2004 | B2 |
6752795 | Cull | Jun 2004 | B2 |
6902542 | Gordon | Jun 2005 | B2 |
6908451 | Brody et al. | Jun 2005 | B2 |
6962488 | Davis et al. | Nov 2005 | B2 |
7083591 | Cionni | Aug 2006 | B2 |
7217257 | Cull et al. | May 2007 | B2 |
7393189 | Davis et al. | Jul 2008 | B2 |
7727179 | Barrett | Jun 2010 | B2 |
7914482 | Urich et al. | Mar 2011 | B2 |
7981074 | Davis et al. | Jul 2011 | B2 |
8092427 | Urich et al. | Jan 2012 | B2 |
8303553 | Kuebler et al. | Nov 2012 | B2 |
8398582 | Gordon et al. | Mar 2013 | B2 |
20020022810 | Urich | Feb 2002 | A1 |
20020128560 | Urich | Sep 2002 | A1 |
20030236508 | Cull | Dec 2003 | A1 |
20040039351 | Barrett | Feb 2004 | A1 |
20050113741 | Huang et al. | May 2005 | A1 |
20060058728 | Urich | Mar 2006 | A1 |
20060058729 | Urich | Mar 2006 | A1 |
20060078448 | Holden | Apr 2006 | A1 |
20060084937 | Akahoshi | Apr 2006 | A1 |
20060100570 | Urich et al. | May 2006 | A1 |
20060173404 | Urich et al. | Aug 2006 | A1 |
20060173426 | Urich et al. | Aug 2006 | A1 |
20060224163 | Sutton | Oct 2006 | A1 |
20060253062 | Liao et al. | Nov 2006 | A1 |
20070106211 | Provost-tine et al. | May 2007 | A1 |
20070179438 | Morgan | Aug 2007 | A1 |
20080167595 | Porter et al. | Jul 2008 | A1 |
20080188792 | Barrett | Aug 2008 | A1 |
20080312594 | Urich | Dec 2008 | A1 |
20100130944 | Music | May 2010 | A1 |
20100152685 | Goh | Jun 2010 | A1 |
20100286651 | Sorensen | Nov 2010 | A1 |
20100305496 | Kuebler et al. | Dec 2010 | A1 |
20100312170 | Maaskamp et al. | Dec 2010 | A1 |
20120157912 | Sorensen et al. | Jun 2012 | A1 |
20120157943 | Sorensen et al. | Jun 2012 | A1 |
Number | Date | Country |
---|---|---|
200151298 | Nov 2005 | AU |
102007031722 | Jan 2009 | DE |
0176681 | Oct 2001 | WO |
0219896 | Mar 2002 | WO |
02019896 | Aug 2002 | WO |
03030717 | Apr 2003 | WO |
03030717 | Mar 2004 | WO |
2004030725 | Apr 2004 | WO |
2007075200 | Jul 2007 | WO |
2009007223 | Jan 2009 | WO |
2009076717 | Jun 2009 | WO |
2012082623 | Jun 2012 | WO |
Entry |
---|
International Searching Authority, International Search Report, PCT/US2011/064423, Apr. 4, 2012, 2 pages. |
International Searching Authority, Written Opinion of the International Searching Authority, PCT/US2011/064423, Apr. 4, 2012, 7 pages. |
Flared Peristaltic Pump Tubing—ICM MS Pump Tubing—Santoprene® Tubing—Flared End Peristaltic Tubing; FlaredTubing.com (Copyright 2009) (3 pages) (see file “Flaredtubing—com”). |
Hausermans abstract from Ophthalmologia Belgica “Breaking the link between vacuum and aspiration flow” (2006). |
Stellaris™ sales brochure “StableChamber—Pack” (Copyright 2007). |
Krieglstein, G.K., et al. (R.N. Weinreb, Douglas D. Koch, and Thomas Kohnen) “Cataract and Refractive Surgery: Progress III”; Essentials in Ophthalmology; published 2009 (Google book search screen images). |
European Patent Office, Extended European Search Report, Application No. 11849053.1, Publication No. 2651354, Jul. 1, 2014, 7 pages. |
Number | Date | Country | |
---|---|---|---|
20120157912 A1 | Jun 2012 | US |
Number | Date | Country | |
---|---|---|---|
61423752 | Dec 2010 | US |