2. Outline
• IOL adjusted using secondary surgical procedures
• IOL adjusted non invasively in post operative setting
• IOL adjusted using femtosecond laser or 2-photon
chemistry
• LAL
3. PO refraction
Brandser et al 45% of 298
emmetropic
within 0.5 D
Murphy et al 72.3% of 1676
eyes
Within 1D 6.4% beyond2D
Mamalis et al. 20% to 40% Incorrect IOL 1& 3-piece
IOLs
4. • Technological inadequacies --incorrect IOL power, AL, corneal
power, A constant
• Mechanical issues (eg, placement of optic in a position
different from expected pre Operative or axis deviation caused
by unwanted rotation of toric IOL
• Unpredictable effects of wound healing on effective lens
position in capsular bag, capsule shrinkage, untreated
astigmatism (preexisting or iatrogenic), procedural or process
mistakes (eg, insertion of wrong IOL or IOL mislabeling by
manufacturer) or any combination of these
• Incorrect corneal measurements
5. Must Demonstrate
• Biocompatibility with intraocular tissues
• Refractive error correction range of approximately 2.0 D
• Precise correction of hyperopic, myopic, & astigmatic
refractive errors to within 0.25 D of target
• Stability of refraction, safe, noninvasive
6. A: Base IOL showing attachment bridge on the
surface of the lens.
B: Front IOL showing haptic that
are designed to fit within the
attachment bridges on the base
IOL surface in piggyback fashion.
C: Assembled multi component IOL.
Adjusted using secondary surgical procedures
Werblin --- 1996
7. Artist's rendition of the multi
component IOL within the capsular bag
Adjusted using secondary surgical procedures
Infinite Vision Optics, A hydrophilic acrylic foldable dual- IOl system
8. Slit lamp photographs 2 years after
• Portaliou et al report a small 2-
year study including 6 adult
patients. Although VA was not a
primary objective UCVA & BCVA
decimal visual acuity improved
from
– 0.11 ± 0.06 (SD) to 0.68 ± 0.11
– 0.28 ± 0.13 to 0.83 ± 0.16
9. The Clarvista Harmoni modular IOL
system Adjusted using secondary surgical
procedures
Hydrophobic, monofocal, or toric, implanted using conventional
phacoemulsification
10. The mechanically adjustable IOL
Acri.Tec AR-1 PC IOL
Adjusted using secondary surgical procedures
an optic PMMA, that is 5.5 mm in diameter & contains two 1.0 mm high cylinder
11. Implantation of the Acri.Tec AR-1 PC
IOL
Adjusted using secondary surgical procedures
12. The AR-1 IOL --tested in human subjects
Adjusted using secondary surgical procedures
• Jahn & Strotmann --- 35 human eyes.
• Adjustment procedure 2 weeks after initial surgery -- 2 eyes
• No difference was seen between a control PMMA IOL & AR-1 IOL in VA,
stabilization of refractive error, signs of inflammatory reaction, & IOP over a mean
follow-up of 9 ± 6 mths.
• Initial adjustment surgery successfully changed mydriatic refraction from 1.0 ± 0.75
D to 0 ± 0.5 D, resulting in a decimal VA of 1.0.
Immediately after implantation 4 weeks after implantation
13. In a longer study of the same cohort
(median followup time of 18months)
Adjusted using secondary surgical procedures
• None of eyes developed signs of inflammation, corneal
decompensation, iris atrophy, pupil distortion,
decentration, spontaneous capsule tearing, or Amsler grid
abnormalities.
• No difference in VA, refractive stability, or IOP was seen between
control IOL & AcriTec IOL.
• PCO -- (18 of 35 eyes), -- Nd:YAG laser posterior capsulotomy,
restored VA in all patients.
• 2 eyes -- adjusted initially continued to show stable refraction with no
complications noted 15 &18 mths postoperatively.
14. Mechanism of adjustment of the
repeatedly adjustable IOL
Adjusted using secondary surgical procedures
The optic can be adjusted anteriorly & posteriorly in a screw-
like fashion within the outer ring
Perspex CQ PMMA matrix
15. Mechanism of adjustment of the
repeatedly adjustable IOL
Adjusted using secondary surgical procedures
Repeatedly adjustable IOL before polishing & sterilization
• Proof-of-concept study involving 27 prototype IOLs
(each with a 14.0 mm haptic outer diameter, 8.46 mm
outer ring diameter & 5.64 mm optic diameter, inner
optic thickness depended on power of IOL & ranged
from 2.0 to 2.5 mm
16. The first magnetically adjustable
IOL
Adjusted noninvasively in postoperative
setting
• Matthews et al Incorporated magnets into repeatedly adjustable IOL.
• 2 separate magnetic components (IOL & external device) forming a
magnetic coupling external device transfers force & torque to IOL
during adjustment procedure.
• The optic is a Perspex CQ PMMA matrix with an embedded magnetic
spindle consisting of samarium cobalt.
• Spindle ring maximum inner diameter - 4.0 mm, 6.0 mm outer
diameter, 2.0 mm thickness so it could be easily embedded in optic
of repeatedly adjustable IOL.
• The external source consists of neodymium-iron- boride permanent
magnets in 2-pole & 4-pole configurations.
17. Magnetic…
Adjusted noninvasively in postoperative setting
• They embedded magnetic spindles into optic of IOL, created
external magnetic source, & showed magnetic source can
turn IOL optic in forward & reverse directions with magnetic
spindles focus to within 0.04 D for a 26.0 D IOL or to within
0.01 D for a 16.0 D IOL.
• Leaching studies were also performed to demonstrate
whether metallic species would leak out of optic over time.
• Over a 1-mth period, concentrations of cobalt & samarium in
balanced salt solution were comparable to that of dissolving
a bare magnet in solution.
18. Wirelessly controlled liquid crystal IOL
Adjusted noninvasively in postoperative setting
A: A cross-section of the liquid crystal
IOL depicting glass substrates (1); low-
ohmic layer (2); liquid crystal (3);
contact (4); and high-ohmic layer (5).
B: Photograph of the liquid crystal IOL
with rectifying diode (R) and antenna
(A) along the outer surface of the lens
19. Wirelessly controlled liquid crystal IOL
Adjusted noninvasively in postoperative setting
The basic design of wireless radiofrequency control unit
consists of
• A computer attached to a setup
• A function generator
• A radiofrequency oscillator
• A modulator
• A radiofrequency amplifier & a transmitting antenna
20. Wirelessly controlled liquid crystal IOL
Adjusted noninvasively in postoperative setting
• The signal (approx 6 MHz) from radiofrequency oscillator
is amplitude modulated by function generator (F = 0 to 50
kHz), amplified & transmitted to liquid crystal modal IOL
via transmitting antenna.
• Once loop-receiving antenna in IOL receives signal, it is
demodulated by rectifier circuit to produce a low
frequency voltage that is then applied to liquid crystal
modal corrector. This allows adjustment of liquid crystal
IOL
21. Wirelessly controlled liquid crystal IOL
Adjusted noninvasively in postoperative setting
• In vitro measurements of a 5.0 mm clear aperture prototype with an
initial focusing power of + 12.5 D remotely driven by a radiofrequency
control unit at approx 6 MHz were carried out using a Hartmann-
Shack wave front sensor.
• The IOL based on a 40 mm thick liquid crystal layer allows an
adjustable defocus of 4 waves, ie, an accommodation of
approximately 2.51 D at a wavelength of 534 nm, & correction of
spherical aberration coefficient ranging from 0.8 to 0.67 waves.
• Frequency switching technique was used to increase response speed.
Full-scale settling time of adaptive modal corrector was measured to
be approximately 4 seconds.
22. Tentative design of an optic that is amenable
to postoperative power adjustment
Iols that can be adjusted using the femtosecond
laser
Intraocular lens (A) consists of concentric rings (B and C) that have connecting
members (E) Localized regions of pockets of heat absorbing material (D) are
placed on the connecting members
23. Application of a photon produced by
a femtosecond laser onto the heat-
absorbable material, resulting in
tension between the concentric rings
of the IOL
Application of a photon produced by a
femtosecond laser onto the connecting
members, resulting in tension relief
between the concentric rings of the IOL.
Iols that can be adjusted using the
femtosecond laser
24. Iols that can be adjusted using the
femtosecond laser
• F Briefly, the femtosecond laser selectively bombards electrons of a
thin 50 mm layer of material embedded within IOL & alters 3-
dimensional shape of material layer, precisely changing its RI &
inducing dioptric power adjustments.
• Using a commercial 2-photon 500 mw femtosecond laser with an
acousto-optic modulator, perfect Lens treated a 1.0 mm diameter
lens (initial power of 1.6 D) that was incorporated into a hydrophobic
acrylic button. Various phase wrapping techniques were used to
accomplish several diopters of refractive change within material.
25. Iols that can be adjusted using the
femtosecond laser
• Phase wrapping is a process in which surface of IOL is divided into
concentric diffractive zones & total IOL power is a summation of
power of each diffractive zone.
• For eg. a single 50 mm layer in a 6.0 mm optic provides up to 5.0 D of
correction, so 4 layers should theoretically provide 20.0 D.
• Tightening diffractive zones along a single axis & changing relative
heights & profiles of refractive zones can provide astigmatic &
aspheric corrections, respectively. Using an acousto-optic modulator,
total in vivo treatment time is estimated to be 20 to 60 sec with this
potentially revolutionary technology.
26. • Change in RI up to 0.03, enables 2.5 D of IOL adjustment
• Rx of astigmatism
• Bombarding coumarin- based polymers with photons of a wavelength
results in dimerization & production of material with higher RI.
• Conversely, application of photons with different wave length results in
reverse reaction & produces material with lower RI.
• Both reactions occur instantaneously & allow immediate postoperative
refraction of patient.
• Sunlight does not carry enough photon
density to disrupt chemical properties of IOL.
Application of 2-photon chemistry on
coumarin-based polymers
27. Micrograting patterns applied by the
femtosecond laser to an IOL optic. A: Pattern as
seen from the anterior view. B: Pattern applied
to a thin layer of material embedded within the
IOL optic; side view
30. LAL
• Developed by Calhoun Vision
• Studies reported in 2003, it has corrected residual refractive errors of
up to 2.0 D of hyperopia, myopia, & astigmatism in patients with
normal, shortened, & elongated & to provide results close to
emmetropia in patients with history of previous laser refractive
surgery.
• It is a foldable 3-piece silicone PC IOL. It is composed of a medical-
grade UV light–filtering silicone optic containing light activated
photointiator & mobile silicone macromers.
2 Weeks Postoperative Of LAL
31. LAL
• The IOL has an overall diameter of 13.0 mm, optic is 6.0 mm in diameter.
The IOL has squared posterior optic edges, round anterior edges, & blue
PMMA modified-C haptics with a posterior optic– haptic 10-degree
angulation.
• These features prevent PCO & rotation of IOL within capsular bag, which
makes IOL suitable for toric correction.
• The IOL has enhanced UV light–filtering material concentrated along
posterior aspect of optic in a layer that measures up to 100 mm.
protection of retina, preventing during overexposure to UV radiation in
300 to 400 nm range during adjustments & lock-in treatments.
32. LAL
• Healing period of 2 -4 weeks
• Patient's refraction & acuity
• 1 or 2 UV-light adjustment procedures, each 2 min, can be adjusted
multiple times
• Lock-in once optimized.
• Material design of LAL is based on principles of photochemistry &
diffusion where by photoreactive components incorporated in
crosslinked silicone lens matrix are photopolymerized on exposure to
UV light (365 nm) of a select spatial irradiance profile.
• Each adjustment provide up to 2.0 D of power correction based on in
vitro studies.
• 1 case report of a 57-year-old woman whose VA declined secondary
to noncompliance highlights need for adequate UV light protection &
appropriate patient compliance.
2 Years After Implantation
35. The LDD
• Slitlamp & a UV-light source in a computer-controlled system. The
light source mercury arc lamp with a narrowband pass interference
filter producing a 365 nm wavelength.
36. The LDD..
• After dilating & anesthetizing patient's eye, surgeon couples a 0.835
contact lens on eye, fixate on a target, aligns a reticle target on edge of
optic, & then applies treatment for specified time.
• Adjustment procedure 40 to150 sec & may vary
• The lock-in lasts for 100 sec, & whole IOL is irradiated with a light beam
of a higher intensity during this procedure.
• Evaluation of LD System using a rabbit model has demonstrated myopic,
hyperopic, & astigmatic adjustments of LAL are possible without any
evidence of corneal or retinal toxicity apparent on slitlamp &
histopathological examinations.
37. DLDD
• Calhoun Vision, Inc. in collaboration with Carl Zeiss Meditec AG,
developed digital light delivery device that allows correction of
spherical error, astigmatism, & HOAs.
• A study of 13 human patients showed the device can reliably deliver
hyperopic & myopic corrections to within 0.25D of intended
outcome.
• The light-adjustable IOL is currently on market in Europe & Mexico &
is in final phase of FDA clinical trials in U.S.
• It is truly a revolutionary technology that creates possibility of
emmetropia for all pseudophakic patients.
by
g
38. Discussion
Mamalis et al Adjustments of LAL
hyperopic, myopic,
astigmatic, & HOA
No postOp clinical changes on
slitlamp examination & no
evidence of toxicity to cornea,
iris, retina, & choroid on
histopathological examination
Calhoun Vision,
Inc
LAL is stable after Nd:YAG
Werner et al corneal endothelial &
retinal safety
Authors applied therapeutic
irradiation dose of lock-in
procedure to 12 cat corneas &
compared
39. Retinal safety study
• In the LAL (which contains a UV-light filter) was placed in 1 eye & a
control silicone IOL without a UV-light filter in the contra lateral eye
of 16 pigmented rabbits.
• 5 times the expected maximum UV-irradiation dosage applied to
study eye & up to 2 times that dosage to control eye.
• Histopathological evaluation revealed no evidence of corneal,
anterior segment, or retinal toxicity in eyes implanted with LAL.
However, 3 of 16 eyes with control IOL demonstrated focal areas of
retinal damage consistent with laser burn.
40. Safety of the UV-irradiation treatment
dosage in humans
Lichtinger et
al
Mean
endothelial
cell loss
10
eyes
12.6% at 1 wk
post op
9.1% , at 6 mths
Hengerer et
al
mean
endothelial
cell loss
122
eyes
6.91% at 2wk
post op
6.57%, at 12 mths
corneal
thickness
6.18% at 2wks
post op
0.64%, at 1 yr
• These values are in line with values for endothelial cell loss due to
phacoemulsification
41. Safety of myopic & hypermetropic
correction
Chayet et al 14 eyes myopic
adjustment of
LAL with LDD
Purposly
implanted IOL
with myopic
error of 1.5 D
1day after locking 13 0.25D
9mths 14 0.50D
Chayet et al 14 eyes Hyperopic
corrections
of LAL
+0.25 D to
+2.00D
1day after locking 13 +0.25D
6mth 14 +0.5D
42. Effective at treating postoperative toric errors
Hengerer et al. mean
sphere
mean
cylinder
within
0.50 D
Within
0.25 D
40 eyes
4 mths
post op
from 0.58 ±
2.29 D to 0.04
± 0.37 D
improved
from 1.02 ±
2.19 D to
0.24 ± 0.40
D
0.88 ± 0.66
D to 0.41 ±
0.25 D
35 of 40
(88%)
24 of 40
(60%)
Chayet et al. 5
patients
with post op cylindrical
refractive errors of 1.25
to 1.75 D
spherical
equivalent
within 0.25 D
20/25 at
9mths
43. 9 of 10
eyes
mean
pre op
refraction
improved
to
1 mth
after lock-
in mean
astigmatis
m
improved
2 eyes
residual
astigmatis
m
3 eyes
residual
astigmatis
m
10
toric
adjustmen
t
+0.78 ±
4.16 D
0.07 ±
0.21 D
0.88 ±
0.77 D
to 0.15 ±
0.20 D,
0.50 D 0.25 D gained at
least 2
lines of
corrected
VA.
Winkler Von Mohrenfels et al
44. Lichtinger et al. performed 1-year follow-up study in 10 eyes (corneal
astigmatism 1.00 D & 2.00 D) adjustment with lock-in was done
Ten of
10
(100%)
-0.50 D of
targeted
cylindrical
adjustment &
cylinder axis
was same in
60%
At 12 mth
stable
within 10◦
of rotation
LAL rotated 3◦
within 10◦
margin of
error for toric
correction
7of 10,
70% eyes
UDVA
≥20/25
10 (100%)
were
>20/32
after 1 yr
Hengerer et al. report a study of 122 eyes that were followed for 18 mths.
Mean
refraction
in SE
improved
from 0.36 ±
2.78 D
preop to
0.03±0.17
At 18 mths post
mean sphere
improved from
0.82 ± 2.74 D to
0.10 ± 0.22 p
Mean cylinder
improved from
0.92 ± 0.66 D to
0.25 ± 0.22 D
All eyes
≥ 20/25
88%
≥ 20/20 of
UDVA
uncorrected distance visual acuity(UDVA)
45. LAL can correct up to 2.25 D in sphere &
2.75 D in cylinder in axial hyperopia &
myopia.
In a 1-year follow-up study by Hengerer et al, 15 eyes with an AL < 22.20
mm (axial hyperopia) received LAL
• 14 of 15 (93%) -- 0.5 D of the targeted refractive adjustment
• 10 of 15 (67%) -- 0.25 D
• 1 of 15 changed > 0.25 D in MRSE
In another 1-year study by Hengerer et al, 21 eyes with an AL longer than
24.5 mm (axialmyopia) received LAL
• 20 of 21 eyes (96%) -- 0.50D of targeted refractive adjustment
• 17 of 21 (81%) were within 0.25 D
• 1 of 21 changed > 0.25 D in MRSE (this eye suffered from tear film
instability) at completion of study
manifest refraction spherical equivalent (MRSE)
46. • One case report LAL was used to treat a traumatic cataract in a 36-yr-old
man with prior LASIK surgery. Following adjustments & lock-ins, patient
achieved an end refraction of + 0.50 D & an UDVA of 20/20.
• Retrospective case series by Brierley shows LAL implantation & post-
implantation adjustment provide precise refractive outcomes in patients
who have had LASIK or PRK.
• In this study, 34 eyes with a history of refractive surgery received LAL.
One wk after lock-in,
• 25 of 34 eyes were within 0.25 D of targeted refraction
• 33 of 34 eyes were within 0.50 D
• 34 of 34 eyes were within 1.00 D
• 19 of 20 (95%) had a UDVA of 20/25
• 20 of 20 eyes had a UDVA of 20/30.
47. • Calhoun Vision's LAL is adjustable IOL is undergoing third & final phase
of FDA clinical trials In USA.
• Compatibility of certain IOLs with imaging techniques such as MRIs
needs to be assessed.
• Femtosecond laser increasing in popularity & its applications to
cataract surgery being extensively researched, this modality may lend
itself well to adjustable IOL technologies.
• Adjustable IOLs, especially those adjusted noninvasively in
postoperative setting, will become a mainstay of IOL implantation
surgery within next few decades.
Editor's Notes
manifest refraction spherical equivalent (MRSE) within 0.25 D of emmetropia, improved their uncorrected distance visual acuity
(UDVA)
Multi component IOL
Mechanically adjustable IOL
Repeatedly adjustable IOL
Despite the many advances in cataract surgery, incorrect intraocular lens (IOL) power remains one of the most frequent causes of IOL exchange. incidence of incorrect IOL power has been decreasing recently, incorrect IOL power remains a significant problem and the issue of persistent refractive error following otherwise successful cataract surgery must be addressed.
Although surgeons have been working diligently to refine the formulas used to predict IOL power preoperatively, a recent paper reported that more than 20 articles
near future, the problem of incorrect IOL power will likely be exacerbated by the rising popularity of laser refractive surgeries, the increasing expectations that patients place on their physicians to give them “perfect” vision, and the arsenal of IOLs currently available.
Before any adjustable IOL becomes available
for patient use, it must demonstrate the following
properties
exchanging only the front part of the IOL, leaving the base part in the capsular bag after implantation. If the initial surgical result is unsatisfactory or if new types of IOLs emerge in the future, the front part of the IOL can be exchanged. spherical, cylindrical, and multifocal corrections needed in 0.25 D power increments
Infinite Vision Optics has developed a hydrophilic acrylic foldable IOL system, dual-IOL system
In this model, the base lens has a plate–haptic configuration that provides only spherical correction, while the front lens has 2 thin lens components held together by hydrostatic forces as a single lens, allowing spherical, cylindrical, and multifocal correction. The base lens sits in the capsular bag as a PC IOL and the front lens has 2 haptics that fit into the small bridges along the anterior surface of the base lens (Figures 1 to 3). The front lens sits in front of the anterior capsule to prevent interlenticular opacification, a well-known complication of
The Infinite Vision IOL has been studied in humans.
enhancement was performed with the IOL multicomponent system. The patient had a refractive surprise of C2.25 D after routine primary surgery with the multicomponent IOL. An enhancement procedure was performed 9 months postoperatively by exchanging the front IOL assembly. This resulted in a final refraction of C0.25 D with a final uncorrected decimal visual acuity of 1.0. the Infinite Vision multi component IOL appears safe and effective in initial studies and it can yield excellent visual outcomes, but the biocompatibility, efficacy, adjustability, and reversibility of this IOL should be assessed in long-term animal and human Nevertheless, the multicomponent IOL technology is promising and may give rise to other innovations such as more advanced front components that can correct higher-order aberrations (HOAs) and new ways of managing a congenital cataract in a child whose ocular anatomy and visual needs are expected to change over time.
hydrophobic , can be monofocal, multifocal, or toric, can be implanted using conventional phacoemulsification procedures through a small incision.
First, the base component can be placed into a standard delivery tool and injected into the capsular bag. Then, through the same incision, the optic can be injected and securely attached to the base by engaging the fixation features via the use of conventional surgical instruments. For toric adjustment, the optic can be rotated into the preferred position also using conventional instruments through either the primary surgical incision or a side-port incision at the time of surgery or at a later date. In the case of a multifocal IOL, the base component allows sliding the optic from side to side to enhance centration on the visual axis. This approach can be leveraged in cases of suboptimal centration relative to the undilated pupil postoperatively and can reduce visual disturbances when present. If at some point the patient develops different refractive needs, the surgeon can remove the optic by disengaging the fixation features and extracting the optic, and he or she can then securely place a new optic within the base component. Currently, there is an ongoing 30- patient randomized control trial using the Harmoni
tested in animal and human eyes. Composed of PMMA, this IOL has an optic that is 5.5 mm in diameter and contains two 1.0 mm high cylinders at the optic–haptic junctions. A piston, attached to the outer part of each haptic, fits within the optic–haptic junction
cylinder, allowing the surgeon to alter the refractive power of the IOL by moving the piston and cylinder relative to each other via a specialized IOL optic
manipulator. This, in turn, allows the optic of the IOL
to move along the optical axis
Figure 5. A: The Acri.Tec AR-1 PC IOL. B: The
piston, which is attached to the haptic, can be
moved relative to the cylinder, which is
attached to the optic, for power adjustment.
C and D depict the instruments used for adjusting
the Acri.Tec AR-1 PC IOL. C: Forceps.
D: Two hooks. Reprinted with permission of
the Journal of Cataract & Refractive Surgery.14
adjustment procedure can be performed several times through 2 corneal paracenteses of 1.0 mm width. The surgeon can move the piston using an optic manipulator with a T-shaped or an L-shaped spike, while using a second manipulator to support the cylinder
from the opposite side, or vice versa, allowing the surgeon to alter the position of the optic in the anterior–posterior direction. With the mechanically adjustable IOL, the surgeon should have an adjustment range of 2.0 to 2.5 D in an eye of average length (1.5 D/mm displacement).
Implantation of the Acri.Tec AR-1
PC IOL (A) and adjustment of the IOL (B) in
a pig cadaver eye. Reprinted with permission
of the Journal of Cataract & Refractive Surgery.14
For patients in whom conventional IOLs will result in high ametropia or anisometropia (ie, those with unilateral cataract and high ametropia), the surgeon can initially set the pseudophakic eye for high ametropia to avoid binocular visual disturbance. After surgery in the second eye, the surgeon can set both eyes for emmetropia to avoid postoperative high spectacle correction
could have application to pediatric ophthalmology as it can be adjusted while the patient&apos;s eye lengthens with age. Jahn et al.14 also claim that with specialized motors, the IOL could serve as a lens prosthesis with full accommodating capacity.
Figure 7. A: Acri.Tec AR-1 PC IOL immediately
after implantation in a rabbit eye. B:
The eye shows no evidence of inflammation
or corneal damage at 4 weeks after implantation.
Reprinted with permission of the Journal
of Cataract & Refractive Surgery.1
The repeatedly adjustable IOL consists of an optic and an outer ring with J-loop haptics, all made of Perspex CQ PMMA matrix. The optic twists anteriorly and posteriorly within the outer ring in a screw-like fashion, providing the basis of postoperative refractive error power adjustments are made via 2 notches on the optic using a Sinskey hook or similar instrument. In a proof-of-concept study involving 27 prototype IOLs (each with a 14.0 mm haptic outer diameter, 8.46 mm outer ring diameter, and 5.64 mm optic diameter; the inner optic thickness depended on the power of the IOL and ranged from 2.0 to 2.5 mm), the authors showed that the rotational forces required for power adjustment stayed well below the target maximum of 1.5 ounce inches in the forward and reverse directions.
correctionFigure 8... Reprinted with permission of the Journal of Cataract & Refractive Surgery.18
Figure 9..
Reprinted with permission of the Journal of Cataract & Refractive
Surgery.18
Figure 10. Wirelessly controlled liquid crystal IOL. A: A cross-section of the liquid crystal IOL depicting glass substrates (1); low-ohmic layer (2); liquid crystal (3); contact (4); and high-ohmic layer (5). B: Photograph of the liquid crystal IOL with rectifying diode (R) and antenna (A) along the outer surface of the lens. Reprinted with permission of Optics Express
Femtosecond laser was introduced in 2001 as a means of creating a corneal flap during LASIK surgery and since then has been used in cataract surgery with applications such as astigmatic limbal relaxing incisions, anterior capsulotomy, and lens fragmentation. Alcon Laboratories, Inc. has patented an IOL that is
amenable to postoperative power adjustment with the femtosecond laser. E Per Alcon&apos;s patent, the tentative design of the IOL consists of an optic containing an internal microstructure with 2 concentric rings connected by members, which may have localized regions or pockets of heat-absorbing material or dye. Application of the pulsatile laser to the heat-absorbing pockets causes shrinkage of the material, increasing tension between the inner and outer rings. In contrast, the connecting members can be broken on laser application, resulting in tension relief between the concentric rings within the IOL
(Figures 11 to 13). Alcon claims
that its IOL can be reshaped at any time postoperatively
and coupled with wavefront aberrometry to
provide excellent refractive results,
Figure 11. Tentative design of an optic that is amenable to postoperative
power adjustment with the use of a femtosecond laser. Intraocular
lens (A) consists of concentric rings (B and C) that have
connecting members (E). Localized regions of pockets of heatabsorbing
material (D) are placed on the connecting members. Based
on Sacharoff A, Karakelle M.E
Based on the same above-mentioned principle
Figure 12Based on Sacharoff and
Karakelle.E
Figure 16lock-in. Photo courtesy of Fritz H. Hengerer,
MD, PhD, Frankfurt am Main, Germany.
Figure 17. The initial LAL had UV light–filtering agents spread throughout the optic to protect the retina from damage during the adjustment and lock-in procedures. However, the next generation light-adjustable IOL features a UV-light enhanced layer (measuring up to 100 mm) on the posterior aspect of the IOL. The light-adjustable IOL is currently undergoing studies to determine whether the number of postoperative adjustment procedures can be decreased by thinning the posteriorly placed UV-light enhanced layer. If so, this would make the light-adjustable IOL more attractive for patients who may not otherwise comply with their physician&apos;s orders to wear UV light–filtering sunglasses for up to 4 weeks postoperatively (courtesy of Calhoun Vision).
Composed of photoinitiator that causes a macromer to polymerize on exposure to spatially profiled UV light & diffusion of unpolymerized macromer to treated or exposed region leads to precise shape change & hence inducement of power change.
This action produces a chemical potential difference between the
Irradiated and unirradiated regions of the lens.
To reestablish thermodynamic equilibrium, macromers from the
unirradiated portion of the lens will diffuse along the
concentration gradient into the photopolymerized
area, inducing a shape change to produce a predictable
refractive power change. For example, if the central
portion of the lens is irradiated, unreacted macromer
from the non irradiated periphery diffuses into the
central irradiated area producing an increase in IOL
power or a hyperopic correction. Conversely, by irradiating
the outer periphery of the IOL, macromer
migrates outward producing a decrease in the power
or a myopic correction
Figure 18. The silicone light-adjustable IOL is shown in cross section. A hyperopic correction is performed by irradiating the central portion of the light-adjustable IOL. This accomplishes a polymerization of photosensitive silicone macromers (pink squiggles) that are embedded within the silicone matrix (green lines). Polymerization of the treated area is indicated by the thick blue lines. Polymerization does not change the light-adjustable IOL power (note same curvature of lens in second frame). However, silicone polymerization does create a concentration gradient between the peripheral untreated portions of the light-adjustable IOL where macromer remains, and the central treated portion of the light-adjustable IOL, which is macromer deplete. Over the next 12 to 18 hours, macromer diffuses down the gradient into the center of the light-adjustable IOL causing the center of the IOL to swell. This increases the power of the IOL. Based on the duration and power of exposure, differing amounts of hyperopia can be corrected. After the desired power change is confirmed (1 day after adjustment), the entire light adjustable IOL is treated to polymerize remaining macromer. This locks in the power so that no further changes occur. In clinical practice, light-adjustable IOL adjustment is performed when spectacles are ordinarily prescribed, 2 to 4 weeks after cataract surgery. Lock-in is performed the following day. Until lock-in, patients wear sunglasses to protect against UV exposure. Following lockin, no protective eyewear is required (courtesy of Calhoun Vision).
Figure 19. To treat myopia, the edges of the light-adjustable IOL are irradiated. Polymerization and consumption of macromer in the light-adjustable IOL periphery causes the silicone macromer to diffuse outward. This reduces the volume of macromer in the central portion of the IOL, resulting in central flattening and reduction of IOL power (courtesy of Calhoun Vision).
Figure 20. The digital light delivery device designed and manufactured
by Carl Zeiss Meditec AG is mounted on a conventional slitlamp.
The refractive error and desired refractive outcome are
entered on the color console and irradiation is activated using a
foot pedal or joystick (courtesy of Calhoun Vision).
Figure 21. Slitlamp photo of an albino New Zealand white rabbit.
The LAL is easily seen in the capsular bag and exhibits excellent centration
without evidence of inflammation or PCO development at
Figure 22. Slitlamp photo of the light-adjustable IOL 2 years after implantation
in a human patient. Again, the IOL appears stable with
excellent centration and no evidence of inflammatory reaction after
2 years of follow-up. Photo courtesy of Fritz H. Hengerer, MD,
PhD, Frankfurt am Main, Germany
Heinzelmann et In this study, 2 pairs of human corneas(which were unsuitable for transplantation but had a good endothelium) were exposed to either light adjustable IOL treatment with a target refraction of the maximum adjustable profile for hyperopia with astigmatism (right corneas) or to the white light of the same slitlamp for identical time frames (left corneas). The authors showed no significant differences in endothelial cell number, morphology, and percentage of necrosis on histopathological examination 6 weeks after UV irradiation
within 0.25 D of emmetropia, improved their
These results are encouraging because despite a wide array of empirical formulas, IOL power remains difficult to predict in those patients. With laser refractive surgery becoming mainstream, a growing number of patients present with a history of PRK or LASIK prior to having their cataract removed. These conditions limit the predictive ability of biometry & keratometry to determine adequate IOL power preoperatively. Fortunately, LAL provides excellent refractive results for these patients.