CA2712972C - Lens delivery system cartridge - Google Patents
Lens delivery system cartridge Download PDFInfo
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- CA2712972C CA2712972C CA2712972A CA2712972A CA2712972C CA 2712972 C CA2712972 C CA 2712972C CA 2712972 A CA2712972 A CA 2712972A CA 2712972 A CA2712972 A CA 2712972A CA 2712972 C CA2712972 C CA 2712972C
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- 238000005304 joining Methods 0.000 claims description 2
- 238000003780 insertion Methods 0.000 abstract description 7
- 230000037431 insertion Effects 0.000 abstract description 7
- 208000027418 Wounds and injury Diseases 0.000 description 23
- 238000002347 injection Methods 0.000 description 6
- 239000007924 injection Substances 0.000 description 6
- 208000014674 injury Diseases 0.000 description 6
- 239000000203 mixture Substances 0.000 description 6
- 230000008733 trauma Effects 0.000 description 6
- 239000000463 material Substances 0.000 description 3
- 229920003229 poly(methyl methacrylate) Polymers 0.000 description 3
- 238000001356 surgical procedure Methods 0.000 description 3
- 230000006835 compression Effects 0.000 description 2
- 238000007906 compression Methods 0.000 description 2
- 210000004087 cornea Anatomy 0.000 description 2
- 238000000034 method Methods 0.000 description 2
- 239000004926 polymethyl methacrylate Substances 0.000 description 2
- 210000001525 retina Anatomy 0.000 description 2
- 206010002945 Aphakia Diseases 0.000 description 1
- 208000002177 Cataract Diseases 0.000 description 1
- 229920006397 acrylic thermoplastic Polymers 0.000 description 1
- 230000007812 deficiency Effects 0.000 description 1
- 230000003292 diminished effect Effects 0.000 description 1
- 201000010099 disease Diseases 0.000 description 1
- 208000037265 diseases, disorders, signs and symptoms Diseases 0.000 description 1
- 238000009826 distribution Methods 0.000 description 1
- 230000008030 elimination Effects 0.000 description 1
- 238000003379 elimination reaction Methods 0.000 description 1
- 239000000017 hydrogel Substances 0.000 description 1
- 238000002513 implantation Methods 0.000 description 1
- 230000002093 peripheral effect Effects 0.000 description 1
- 229920003023 plastic Polymers 0.000 description 1
- 239000004033 plastic Substances 0.000 description 1
- 229920001296 polysiloxane Polymers 0.000 description 1
- 238000005096 rolling process Methods 0.000 description 1
- 238000004904 shortening Methods 0.000 description 1
- 239000007787 solid Substances 0.000 description 1
- ISXSCDLOGDJUNJ-UHFFFAOYSA-N tert-butyl prop-2-enoate Chemical compound CC(C)(C)OC(=O)C=C ISXSCDLOGDJUNJ-UHFFFAOYSA-N 0.000 description 1
- 230000007704 transition Effects 0.000 description 1
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/14—Eye parts, e.g. lenses, corneal implants; Implanting instruments specially adapted therefor; Artificial eyes
- A61F2/16—Intraocular lenses
- A61F2/1662—Instruments for inserting intraocular lenses into the eye
- A61F2/1664—Instruments for inserting intraocular lenses into the eye for manual insertion during surgery, e.g. forceps-like instruments
Abstract
A cartridge for an IOL delivery system (10) that has an injector tip (12) geometry designed to reduce stresses at the incision wound edges generated during insertion of an IOL into an eye.
Description
LENS DELIVERY SYSTEM CARTRIDGE
This invention relates to intraocular lenses (IOLs) and more particularly to cartridges for use with devices used to inject IOLs into an eye.
Background of the Invention The human eye in its simplest terms functions to provide vision by transmitting and refracting light through a clear outer portion called the cornea, and further focusing the image by way of the lens onto the retina at the back of the eye. The quality of the focused image depends on many factors including the size, shape and length of the eye, and the shape and transparency of the cornea and lens.
When trauma, age or disease cause the lens to become less transparent, vision deteriorates because of the diminished light which can be transmitted to the retina. This deficiency in the lens of the eye is medically known as a cataract. The treatment for this condition is surgical removal of the lens and implantation of an artificial lens or IOL.
While early IOLs were made from hard plastic, such as polymethylmethacrylate (PMMA), soft, foldable IOLs made from silicone, soft acrylics and hydrogels have become increasingly popular because of the ability to fold or roll these soft lenses and insert them through a smaller incision. Several methods of rolling or folding the lenses are used. One popular method is an injector cartridge that folds the lenses and provides a relatively small diameter lumen through which the lens may be pushed into the eye, usually by a soft tip plunger. The most commonly used injector cartridge design is illustrated in U.S. Patent No. 4,681,102 (Bartell), and includes a split, longitudinally 3o hinged cartridge. Similar designs are illustrated in U.S. Patent Nos.
5,494,484 and 5,499,987 (Feingold) and 5,616,148 and 5,620,450 (Eagles, et al.). In an attempt to avoid the claims of U.S. Patent No. 4,681,102, several solid cartridges have been investigated, see for example U.S. Patent No. 5,275,604 (Rheinish, et al.) and 5,653,715 (Reich, et al.).
These prior art devices were intended to inject an IOL into the posterior chamber of an aphakic eye through a relatively large (approximately 3.0 mm or larger) incision.
Surgical techniques and IOLs have been developed that allow the entire surgical procedure to be performed through much smaller incisions, 2.4 mm and smaller.
Such small incisions require that the IOL be compressed very tightly, and that the nozzle used on the injection cartridge have very thin walls. The combination of a tightly compressed lens traveling through a very thin walled nozzle often results in the nozzle splitting during use. In addition, although the surgeon may make the incision a specific size, insertion and manipulation of the cartridge and the lens frequently stresses the incision walls, increasing the size of the incision as well as causing trauma to the surrounding tissue.
Accordingly, a need continues to exist for an intraocular lens injection cartridge capable of injection an IOL through a relatively small incision with reduced trauma to the tissue.
This invention relates to intraocular lenses (IOLs) and more particularly to cartridges for use with devices used to inject IOLs into an eye.
Background of the Invention The human eye in its simplest terms functions to provide vision by transmitting and refracting light through a clear outer portion called the cornea, and further focusing the image by way of the lens onto the retina at the back of the eye. The quality of the focused image depends on many factors including the size, shape and length of the eye, and the shape and transparency of the cornea and lens.
When trauma, age or disease cause the lens to become less transparent, vision deteriorates because of the diminished light which can be transmitted to the retina. This deficiency in the lens of the eye is medically known as a cataract. The treatment for this condition is surgical removal of the lens and implantation of an artificial lens or IOL.
While early IOLs were made from hard plastic, such as polymethylmethacrylate (PMMA), soft, foldable IOLs made from silicone, soft acrylics and hydrogels have become increasingly popular because of the ability to fold or roll these soft lenses and insert them through a smaller incision. Several methods of rolling or folding the lenses are used. One popular method is an injector cartridge that folds the lenses and provides a relatively small diameter lumen through which the lens may be pushed into the eye, usually by a soft tip plunger. The most commonly used injector cartridge design is illustrated in U.S. Patent No. 4,681,102 (Bartell), and includes a split, longitudinally 3o hinged cartridge. Similar designs are illustrated in U.S. Patent Nos.
5,494,484 and 5,499,987 (Feingold) and 5,616,148 and 5,620,450 (Eagles, et al.). In an attempt to avoid the claims of U.S. Patent No. 4,681,102, several solid cartridges have been investigated, see for example U.S. Patent No. 5,275,604 (Rheinish, et al.) and 5,653,715 (Reich, et al.).
These prior art devices were intended to inject an IOL into the posterior chamber of an aphakic eye through a relatively large (approximately 3.0 mm or larger) incision.
Surgical techniques and IOLs have been developed that allow the entire surgical procedure to be performed through much smaller incisions, 2.4 mm and smaller.
Such small incisions require that the IOL be compressed very tightly, and that the nozzle used on the injection cartridge have very thin walls. The combination of a tightly compressed lens traveling through a very thin walled nozzle often results in the nozzle splitting during use. In addition, although the surgeon may make the incision a specific size, insertion and manipulation of the cartridge and the lens frequently stresses the incision walls, increasing the size of the incision as well as causing trauma to the surrounding tissue.
Accordingly, a need continues to exist for an intraocular lens injection cartridge capable of injection an IOL through a relatively small incision with reduced trauma to the tissue.
2 Brief Summary of the Invention The present invention improves upon the prior art by providing a cartridge for an IOL delivery system that has a injector tip geometry designed to reduce applied stresses on the incision during insertion of the cartridge tip through the wound to reduce the likelihood of tearing or overstretching the wound during cartridge tip insertion and residence time in the wound while the lens is being delivered into the eye.
It is accordingly an objective of the present invention to provide a cartridge for a o lens delivery system that has an injector tip geometry designed to reduce stresses on the wound incision.
It is a further objective of the present invention to provide a cartridge for a lens delivery system that reduces post insertion wound trauma.
In one particular embodiment there is provided an intraocular lens delivery system cartridge, comprising: a body; and a tubular nozzle connected to the body and projecting distally from the body, the nozzle having a cross-section, the cross-section defined by: a portion of an ellipse disposed in the first quadrant and the second quadrant of a Cartesian coordinate system and having a center that is offset from the origin of the Cartesian coordinate system, the portion of the ellipse defined as a first curve; a second curve defined as a mirror image of the first curve mirrored about the abscissa axis of the Cartesian coordinate system, the first curve and the second curve forming first and second points at locations where the first curve and the second curve intersect the abscissa axis of the Cartesian coordinate system; and circular arcs formed at opposing ends of the cross-section proximate the first and second points, each circular arc defined as a portion of a circle joining the first curve and the second curve that is tangent to both the first curve and the second curve and that has a 90 degree tangent line at a location along the abscissa axis crossed by the circular arc.
It is accordingly an objective of the present invention to provide a cartridge for a o lens delivery system that has an injector tip geometry designed to reduce stresses on the wound incision.
It is a further objective of the present invention to provide a cartridge for a lens delivery system that reduces post insertion wound trauma.
In one particular embodiment there is provided an intraocular lens delivery system cartridge, comprising: a body; and a tubular nozzle connected to the body and projecting distally from the body, the nozzle having a cross-section, the cross-section defined by: a portion of an ellipse disposed in the first quadrant and the second quadrant of a Cartesian coordinate system and having a center that is offset from the origin of the Cartesian coordinate system, the portion of the ellipse defined as a first curve; a second curve defined as a mirror image of the first curve mirrored about the abscissa axis of the Cartesian coordinate system, the first curve and the second curve forming first and second points at locations where the first curve and the second curve intersect the abscissa axis of the Cartesian coordinate system; and circular arcs formed at opposing ends of the cross-section proximate the first and second points, each circular arc defined as a portion of a circle joining the first curve and the second curve that is tangent to both the first curve and the second curve and that has a 90 degree tangent line at a location along the abscissa axis crossed by the circular arc.
3 _ Other objectives, features and advantages of the present invention will become apparent with reference to the drawings, and the following description of the drawings and claims.
3a Brief Description of the Drawings Figure 1 is a graph comparing the arc length for a circle, an ellipse and a straight line;Figure 2 is a graph illustrating theoretical incision size for various tip sizes;
Figure 3 is an enlarged perspective view of the lens delivery system cartridge of the present invention; and Figure 4 is a graph showing the blend radius at the point of inflection.
3a Brief Description of the Drawings Figure 1 is a graph comparing the arc length for a circle, an ellipse and a straight line;Figure 2 is a graph illustrating theoretical incision size for various tip sizes;
Figure 3 is an enlarged perspective view of the lens delivery system cartridge of the present invention; and Figure 4 is a graph showing the blend radius at the point of inflection.
4 Detailed Description of the Preferred Embodiments The present invention is directed to cartridge 10 having tip 12, tip 12 having a geometry designed to reduce stresses generated during insertion of an IOL into an eye.
Although any incision size can be used, the dimensions given in the following discussion are based on a 2.0 mm incision or wound in the eye.
The action of inserting a cartridge tip 12 through an incision wound develops to stresses at the wound edges that can result in trauma and tearing of the incision. The inventors have discovered that a correlation exists between the degree of wound stresses and cartridge tip geometry. Based on this discovery, the inventors determined that the incision or wound can be modeled as a deformable body having roughly an elliptical outer dimension with a major axis of approximately 2.0 mm and a minor axis of approximately 0.25 mm. In addition, the inventors determined that a cartridge tip 12 nozzle can be modeled as a rigid body with the assumption that no deformation of the tip 12 nozzle occurs during the insertion of an IOL into an eye and that any deformation occurs in the wound. As no actual tissue material properties are available, the material properties of the wound tissue can be modeled using the Arruda-Boyce material model.
Assuming that the area of the tip 12 nozzle is larger than the area of the wound, the inventors applied a theoretical load to the inside of the wound to "stretch"
the wound large enough to allow the nozzle tip 12 to enter. By lowering the theoretical load until the interior wound margins contact the entire outer peripheral surface of the tip 12, the residual strain, stress, stress distribution and contact pressure can be determined.
One skilled in the art understands that a circle or round cartridge tip has an aspect ratio of 1 because the height and width are equal. However, as the aspect ratio is reduced by shortening the height, the arc length changes which serves to reduce the degree of wound stretching by reducing the applied stresses at the wound edges as shown in FIG 1.
One skilled in the art also understands that a straight line connecting height and width
Although any incision size can be used, the dimensions given in the following discussion are based on a 2.0 mm incision or wound in the eye.
The action of inserting a cartridge tip 12 through an incision wound develops to stresses at the wound edges that can result in trauma and tearing of the incision. The inventors have discovered that a correlation exists between the degree of wound stresses and cartridge tip geometry. Based on this discovery, the inventors determined that the incision or wound can be modeled as a deformable body having roughly an elliptical outer dimension with a major axis of approximately 2.0 mm and a minor axis of approximately 0.25 mm. In addition, the inventors determined that a cartridge tip 12 nozzle can be modeled as a rigid body with the assumption that no deformation of the tip 12 nozzle occurs during the insertion of an IOL into an eye and that any deformation occurs in the wound. As no actual tissue material properties are available, the material properties of the wound tissue can be modeled using the Arruda-Boyce material model.
Assuming that the area of the tip 12 nozzle is larger than the area of the wound, the inventors applied a theoretical load to the inside of the wound to "stretch"
the wound large enough to allow the nozzle tip 12 to enter. By lowering the theoretical load until the interior wound margins contact the entire outer peripheral surface of the tip 12, the residual strain, stress, stress distribution and contact pressure can be determined.
One skilled in the art understands that a circle or round cartridge tip has an aspect ratio of 1 because the height and width are equal. However, as the aspect ratio is reduced by shortening the height, the arc length changes which serves to reduce the degree of wound stretching by reducing the applied stresses at the wound edges as shown in FIG 1.
One skilled in the art also understands that a straight line connecting height and width
5 results in the shortest distance between those points and represents the shortest "arc"
length possible relative to applied stresses on the wound without creating a negative arc.
Negative arc is undesirable because lens damage or undesirable folding can occur when a negative arc or non-curved geometry is used.
The cross-sectional form of an ellipsoid, representing the injection tip 12 geometry, can be analyzed by using the ellipse shape factor. This shape factor `E' can remain constant to maintain the same form as the tip size is varied from 3.0 mm and below. By varying other parameter values, the form is maintained while reducing the periphery and resultant theoretical incision size as shown in Table 1 below and FIG. 2.
This shape factor s, also known as eccentricity, is further discussed below starting with the ellipse equation. A cross section of an ellipsoid in a plane parallel to coordinate axes forms an ellipse. In general, this 2D ellipse can be represented by the following equation:
¨ (y¨ k)2 ,=;
a2 b2 Where h, k represent the center of the ellipse, 'a' is the major axis and 13' the minor axis.
The shape of an ellipse can be represented by its eccentricity, c, defined as follows:
= / a)(Va 2 _b2);
where 0<c<1. The larger the value of s is, the larger the ratio of a to b and the more elongated the ellipse becomes. Furthermore, for a given eccentricity value, if we know parameter 'a' or `1,' then the other parameter can be easily calculated using this equation.
For completion, note that parameters 'a' and '13' are constrained by the following equation:
c2 = a2 b2 ;
length possible relative to applied stresses on the wound without creating a negative arc.
Negative arc is undesirable because lens damage or undesirable folding can occur when a negative arc or non-curved geometry is used.
The cross-sectional form of an ellipsoid, representing the injection tip 12 geometry, can be analyzed by using the ellipse shape factor. This shape factor `E' can remain constant to maintain the same form as the tip size is varied from 3.0 mm and below. By varying other parameter values, the form is maintained while reducing the periphery and resultant theoretical incision size as shown in Table 1 below and FIG. 2.
This shape factor s, also known as eccentricity, is further discussed below starting with the ellipse equation. A cross section of an ellipsoid in a plane parallel to coordinate axes forms an ellipse. In general, this 2D ellipse can be represented by the following equation:
¨ (y¨ k)2 ,=;
a2 b2 Where h, k represent the center of the ellipse, 'a' is the major axis and 13' the minor axis.
The shape of an ellipse can be represented by its eccentricity, c, defined as follows:
= / a)(Va 2 _b2);
where 0<c<1. The larger the value of s is, the larger the ratio of a to b and the more elongated the ellipse becomes. Furthermore, for a given eccentricity value, if we know parameter 'a' or `1,' then the other parameter can be easily calculated using this equation.
For completion, note that parameters 'a' and '13' are constrained by the following equation:
c2 = a2 b2 ;
6
7 PCT/US2009/033401 where `( c,0)' represent the foci of the ellipse. Note that the cross section of the ellipse is modified in the sense that the center of the ellipse is not necessarily at the origin and is allowed to float. However, allowing for de-centration of the ellipse leaves a point of inflection, a sharp feature, when the part of the ellipse lying in quadrant I
is revolved around the x-axis. To smooth out this point, a blend in radius is used so that the tangent to the point intersecting the x-axis is at 90 degrees. These two features, the decentered ellipse as well as a blend radius constitute the cross section of the modified ellipsoid configuration.
An alternate form to the above ellipse equation can be represented as, Ax2 + Bxy + Cy2 + Dx + Ey + F = 0 ;
where B2 < 4AC and all coefficients are real. This equation can be converted to the first equation by completing squares and obtaining a form that displays the center of the ellipse as well as the lengths of major and minor axes.
Using the above guidelines, these parameters can be calculated. The elliptic curve in quadrant 1 was fitted to a general ellipse and it was found that (h, k) =
(0.0,-0.13), and (a, b) = (0.95, 0.72). The eccentricity was then calculated to be 0.65. Given this eccentricity, if either of the two axial dimensions of the ellipse is to be changed, then the other can be calculated with the above equation. Generally, the blend radius at the point of inflection can be chosen to be the smallest possible circle that is tangent to both the curve above and below and has a 90 deg. tangent line at the point crossing the x-axis, such as circle 100 of FIGURE 4.
An example of the application of the determined minimum arc length, aspect ratio and blend radius described above can be seen in Table 1 below where typical values for each of the variables are shown. The table defines typical modified ellipsoid values as a function of incision size. Incision sizes of 1.0, 2.0 and 3.0mm are used to demonstrate the relationship when the ArcLength width and Ellipse eccentricity are held constant.
Applying these values to cartridge tip designs result in the maximum internal volume relative to the minimum arc length which in combination results in significantly reduced strain at the incision wound edges while minimizing the degree of lens compression and resultant lens injection forces.
Table 1: Modified Ellipsoid typical dimensions as a function of Incision size.
Incision Ellipse Major Ellipse Minor Ellipse ArcLength ArcLength Blend Size (mm) Axis, a (min) Axis, b (mm) Eccentricity, (mm) /Width Radius (mm) 1.0 0.392 0.30 0.65 1.087 1.386 0.2 2.0 0.784 0.60 0.65 2.174 1.386 0.4 3.0 1.176 0.90 0.65 3.261 1.386 0.6 The steps outlined above result in a design for cartridge tip 12 that provides the maximum internal volume relative to the minimum arc length. This combination results in significantly reduced strain at the incision wound edges while minimizing the degree of lens compression and resultant lens injection forces. The invention described within provides injector cartridge 10 or nozzle tip 12 shape that reduces the force required to insert cartridge tip 12 through the wound due to the reduced aspect ratio and arc length.
In addition, this curved form facilitates reduced wound trauma and potential for lens damage through elimination of sharp external and internal features or transition points.
While certain embodiments of the present invention have been described above, these descriptions are given for purposes of illustration and explanation. The scope of the claims should not be limited to the embodiments set forth but should be given the broadest interpretation consistent with the description as a whole.
is revolved around the x-axis. To smooth out this point, a blend in radius is used so that the tangent to the point intersecting the x-axis is at 90 degrees. These two features, the decentered ellipse as well as a blend radius constitute the cross section of the modified ellipsoid configuration.
An alternate form to the above ellipse equation can be represented as, Ax2 + Bxy + Cy2 + Dx + Ey + F = 0 ;
where B2 < 4AC and all coefficients are real. This equation can be converted to the first equation by completing squares and obtaining a form that displays the center of the ellipse as well as the lengths of major and minor axes.
Using the above guidelines, these parameters can be calculated. The elliptic curve in quadrant 1 was fitted to a general ellipse and it was found that (h, k) =
(0.0,-0.13), and (a, b) = (0.95, 0.72). The eccentricity was then calculated to be 0.65. Given this eccentricity, if either of the two axial dimensions of the ellipse is to be changed, then the other can be calculated with the above equation. Generally, the blend radius at the point of inflection can be chosen to be the smallest possible circle that is tangent to both the curve above and below and has a 90 deg. tangent line at the point crossing the x-axis, such as circle 100 of FIGURE 4.
An example of the application of the determined minimum arc length, aspect ratio and blend radius described above can be seen in Table 1 below where typical values for each of the variables are shown. The table defines typical modified ellipsoid values as a function of incision size. Incision sizes of 1.0, 2.0 and 3.0mm are used to demonstrate the relationship when the ArcLength width and Ellipse eccentricity are held constant.
Applying these values to cartridge tip designs result in the maximum internal volume relative to the minimum arc length which in combination results in significantly reduced strain at the incision wound edges while minimizing the degree of lens compression and resultant lens injection forces.
Table 1: Modified Ellipsoid typical dimensions as a function of Incision size.
Incision Ellipse Major Ellipse Minor Ellipse ArcLength ArcLength Blend Size (mm) Axis, a (min) Axis, b (mm) Eccentricity, (mm) /Width Radius (mm) 1.0 0.392 0.30 0.65 1.087 1.386 0.2 2.0 0.784 0.60 0.65 2.174 1.386 0.4 3.0 1.176 0.90 0.65 3.261 1.386 0.6 The steps outlined above result in a design for cartridge tip 12 that provides the maximum internal volume relative to the minimum arc length. This combination results in significantly reduced strain at the incision wound edges while minimizing the degree of lens compression and resultant lens injection forces. The invention described within provides injector cartridge 10 or nozzle tip 12 shape that reduces the force required to insert cartridge tip 12 through the wound due to the reduced aspect ratio and arc length.
In addition, this curved form facilitates reduced wound trauma and potential for lens damage through elimination of sharp external and internal features or transition points.
While certain embodiments of the present invention have been described above, these descriptions are given for purposes of illustration and explanation. The scope of the claims should not be limited to the embodiments set forth but should be given the broadest interpretation consistent with the description as a whole.
8
Claims (3)
1. An intraocular lens delivery system cartridge, comprising:
a body; and a tubular nozzle connected to the body and projecting distally from the body, the nozzle having a cross-section, the cross-section defined by:
a portion of an ellipse disposed in the first quadrant and the second quadrant of a Cartesian coordinate system and having a center that is offset from the origin of the Cartesian coordinate system, the portion of the ellipse defined as a first curve;
a second curve defined as a mirror image of the first curve mirrored about the abscissa axis of the Cartesian coordinate system, the first curve and the second curve forming first and second points at locations where the first curve and the second curve intersect the abscissa axis of the Cartesian coordinate system; and circular arcs formed at opposing ends of the cross-section proximate the first and second points, each circular arc defined as a portion of a circle joining the first curve and the second curve that is tangent to both the first curve and the second curve and that has a 90 degree tangent line at a location along the abscissa axis crossed by the circular arc.
a body; and a tubular nozzle connected to the body and projecting distally from the body, the nozzle having a cross-section, the cross-section defined by:
a portion of an ellipse disposed in the first quadrant and the second quadrant of a Cartesian coordinate system and having a center that is offset from the origin of the Cartesian coordinate system, the portion of the ellipse defined as a first curve;
a second curve defined as a mirror image of the first curve mirrored about the abscissa axis of the Cartesian coordinate system, the first curve and the second curve forming first and second points at locations where the first curve and the second curve intersect the abscissa axis of the Cartesian coordinate system; and circular arcs formed at opposing ends of the cross-section proximate the first and second points, each circular arc defined as a portion of a circle joining the first curve and the second curve that is tangent to both the first curve and the second curve and that has a 90 degree tangent line at a location along the abscissa axis crossed by the circular arc.
2. The cartridge of claim 1, wherein the cross-section has an ellipse eccentricity of 0.65.
3. The cartridge of claim 1, wherein a distance along the abscissa axis between locations where the circular arcs intersect the abscissa axis defines a width of the cross-section, wherein a first segment of the cross-section comprises a portion of one of the circular arcs extending from the abscissa axis to the first curve, a portion of the first curve extending between the circular arcs, and a portion of the other of the circular arcs extending from the first curve to the abscissa axis, wherein a length of the first segment of the cross-section defines an arc length, and wherein a ratio of the arc length to the width of the cross-section is 1.386.9
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US2680508P | 2008-02-07 | 2008-02-07 | |
| US61/026,805 | 2008-02-07 | ||
| PCT/US2009/033401 WO2009100337A1 (en) | 2008-02-07 | 2009-02-06 | Lens delivery system cartridge |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2712972A1 CA2712972A1 (en) | 2009-08-13 |
| CA2712972C true CA2712972C (en) | 2013-05-28 |
Family
ID=40677586
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA2712972A Active CA2712972C (en) | 2008-02-07 | 2009-02-06 | Lens delivery system cartridge |
Country Status (15)
| Country | Link |
|---|---|
| US (1) | US8894664B2 (en) |
| EP (1) | EP2254509B1 (en) |
| JP (1) | JP5204247B2 (en) |
| KR (1) | KR101264267B1 (en) |
| CN (1) | CN101938956B (en) |
| AU (1) | AU2009212211B2 (en) |
| BR (1) | BRPI0907725B8 (en) |
| CA (1) | CA2712972C (en) |
| ES (1) | ES2566542T3 (en) |
| IL (1) | IL207163A (en) |
| MX (1) | MX2010008552A (en) |
| NZ (1) | NZ586950A (en) |
| RU (1) | RU2470612C2 (en) |
| WO (1) | WO2009100337A1 (en) |
| ZA (1) | ZA201005386B (en) |
Families Citing this family (22)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US8460375B2 (en) | 2006-08-14 | 2013-06-11 | Novartis Ag | Lens delivery system |
| US9522061B2 (en) * | 2007-02-15 | 2016-12-20 | Novartis Ag | Lens delivery system |
| US20080255577A1 (en) * | 2007-04-11 | 2008-10-16 | Downer David A | Lens Delivery System Cartridge and Method of Manufacture |
| US9610155B2 (en) | 2008-07-23 | 2017-04-04 | Powervision, Inc. | Intraocular lens loading systems and methods of use |
| US8968396B2 (en) | 2007-07-23 | 2015-03-03 | Powervision, Inc. | Intraocular lens delivery systems and methods of use |
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2009
- 2009-02-06 MX MX2010008552A patent/MX2010008552A/en active IP Right Grant
- 2009-02-06 EP EP09707316.7A patent/EP2254509B1/en active Active
- 2009-02-06 RU RU2010137103/14A patent/RU2470612C2/en active
- 2009-02-06 CA CA2712972A patent/CA2712972C/en active Active
- 2009-02-06 ES ES09707316.7T patent/ES2566542T3/en active Active
- 2009-02-06 BR BRPI0907725A patent/BRPI0907725B8/en active IP Right Grant
- 2009-02-06 JP JP2010546051A patent/JP5204247B2/en active Active
- 2009-02-06 AU AU2009212211A patent/AU2009212211B2/en active Active
- 2009-02-06 NZ NZ586950A patent/NZ586950A/en not_active IP Right Cessation
- 2009-02-06 US US12/366,767 patent/US8894664B2/en active Active
- 2009-02-06 WO PCT/US2009/033401 patent/WO2009100337A1/en active Application Filing
- 2009-02-06 CN CN2009801044127A patent/CN101938956B/en active Active
- 2009-02-06 KR KR1020107019706A patent/KR101264267B1/en active IP Right Grant
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- 2010-07-28 ZA ZA2010/05386A patent/ZA201005386B/en unknown
Also Published As
| Publication number | Publication date |
|---|---|
| BRPI0907725B1 (en) | 2019-12-24 |
| RU2470612C2 (en) | 2012-12-27 |
| CA2712972A1 (en) | 2009-08-13 |
| NZ586950A (en) | 2013-01-25 |
| KR20100112639A (en) | 2010-10-19 |
| AU2009212211B2 (en) | 2013-03-14 |
| BRPI0907725B8 (en) | 2023-04-04 |
| EP2254509A1 (en) | 2010-12-01 |
| AU2009212211A1 (en) | 2009-08-13 |
| IL207163A (en) | 2012-07-31 |
| IL207163A0 (en) | 2010-12-30 |
| ZA201005386B (en) | 2011-11-30 |
| CN101938956B (en) | 2013-12-18 |
| RU2010137103A (en) | 2012-03-20 |
| BRPI0907725A2 (en) | 2017-06-13 |
| US20090204123A1 (en) | 2009-08-13 |
| MX2010008552A (en) | 2010-10-25 |
| US8894664B2 (en) | 2014-11-25 |
| JP2011511672A (en) | 2011-04-14 |
| CN101938956A (en) | 2011-01-05 |
| JP5204247B2 (en) | 2013-06-05 |
| ES2566542T3 (en) | 2016-04-13 |
| WO2009100337A1 (en) | 2009-08-13 |
| KR101264267B1 (en) | 2013-05-22 |
| EP2254509B1 (en) | 2016-01-06 |
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