U.S. patent application number 08/942274 was filed with the patent office on 2002-05-23 for method and apparatus for tissue remodeling.
Invention is credited to KNOWLTON, EDWARD W..
Application Number | 20020062142 08/942274 |
Document ID | / |
Family ID | 25477843 |
Filed Date | 2002-05-23 |
United States Patent
Application |
20020062142 |
Kind Code |
A1 |
KNOWLTON, EDWARD W. |
May 23, 2002 |
METHOD AND APPARATUS FOR TISSUE REMODELING
Abstract
An apparatus is provided that modifies a skin surface or a soft
tissue. The apparatus includes a skin surface conforming member and
a hydration delivery device coupled to the conforming member. The
hydration delivery device delivers a hydration agent to the skin
surface. An energy delivery device is coupled to the conforming
member and provides a controlled delivery of energy to the skin
surface.
Inventors: |
KNOWLTON, EDWARD W.;
(DANVILLE, CA) |
Correspondence
Address: |
WILSON SONSINI GOODRICH & ROSATI
650 PAGE MILL ROAD
PALO ALTO
CA
943041050
|
Family ID: |
25477843 |
Appl. No.: |
08/942274 |
Filed: |
September 30, 1997 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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08942274 |
Sep 30, 1997 |
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08827237 |
Mar 28, 1997 |
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08827237 |
Mar 28, 1997 |
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08583815 |
Jan 5, 1996 |
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08583815 |
Jan 5, 1996 |
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08435822 |
May 5, 1995 |
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08583815 |
Jan 5, 1996 |
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08825445 |
Mar 28, 1997 |
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08583815 |
Jan 5, 1996 |
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08825443 |
Mar 28, 1997 |
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60023377 |
Aug 6, 1996 |
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Current U.S.
Class: |
607/99 ;
607/104 |
Current CPC
Class: |
A61N 5/04 20130101; A61B
2018/0047 20130101; A61H 9/005 20130101; A61B 2018/00488 20130101;
A61N 1/403 20130101; A61B 90/02 20160201; A61N 1/30 20130101; A61N
1/28 20130101; A61B 2018/00523 20130101; A61H 9/0071 20130101; A61N
5/0616 20130101; A61B 18/12 20130101; A61B 18/00 20130101; A61F
2/12 20130101; A61B 2018/0066 20130101; A61B 18/1206 20130101; A61B
18/14 20130101; A61B 2018/00452 20130101; A61N 2005/0645 20130101;
A61B 18/203 20130101; A45D 44/22 20130101 |
Class at
Publication: |
607/99 ;
607/104 |
International
Class: |
A61B 018/04; A61F
007/00; A61F 007/12 |
Claims
1. An apparatus for modifying a skin surface or a soft tissue
structure underlying a skin surface, comprising: a skin surface
conforming member with a skin interface surface; a hydration
delivery device coupled to the skin interface surface configured to
deliver a hydration agent to the skin surface; and an energy
delivery device coupled to the conforming member and providing a
controlled delivery of energy to the skin surface.
2. The apparatus of claim 1, further comprising: a hydration sensor
coupled to the conforming member.
3. The apparatus of claim 1, wherein the hydration delivery device
includes a hydraulic pressure source.
4. The apparatus of claim 3, wherein the hydration pressure source
is a mechanical source.
5. The apparatus of claim 3, wherein the hydration delivery device
is an electrical source.
6. The apparatus of claim 3, wherein the hydration delivery device
is a thermal source.
7. The apparatus of claim 3, wherein the hydration delivery device
is a chemical source.
8. The apparatus of claim 7, wherein the chemical source is
ethylene glycol.
9. The apparatus of claim 3, wherein the hydration pressure source
is a diffusion gradient.
10. The apparatus of claim 3, wherein the hydration pressure source
is a compression source.
11. The apparatus of claim 1, wherein the skin surface conforming
member applies a mechanical force to the soft tissue structure.
12. The apparatus of claim 1, further comprising: a feedback
control device coupled the skin surface conforming member.
13. The apparatus of claim 1, further comprising: a surface
pressure sensor coupled to the skin surface conforming member.
14. The apparatus of claim 1, further comprising: a hydraulic
pressure sensor coupled to the skin surface conforming member.
15. The apparatus of claim 1, further comprising: an impedance
sensor coupled to the skin surface conforming member.
16. The apparatus of claim 1, further comprising: a surface
temperature sensor coupled to the skin surface conforming
member.
17. The apparatus of claim 1, wherein the energy delivery device
provides a controlled delivery of energy to the skin surface not
exceeding 1000 joules/cm2 during a single treatment session.
18. The apparatus of claim 1, wherein the energy delivery device
provides a controlled delivery of energy to the skin surface not
exceeding 600 joules/cm2 during a single treatment session.
19. The apparatus of claim 1, wherein the energy delivery device
provides a controlled delivery of energy to the skin surface not
exceeding 200 joules/cm2 during a single treatment session.
20. The apparatus of claim 1, wherein the energy delivery device
provides a controlled dose rate of energy to the skin surface not
exceeding 6 joules/sec/cm2.
21. The apparatus of claim 1, wherein the energy delivery device
provides a controlled dose rate energy to the skin surface not
exceeding 2 joules/sec/cm2.
22. The apparatus of claim 1, wherein the energy delivery device
provides a controlled delivery of energy to a skin surface to
operate in an mpedance range at the skin surface of 70 ohms cm2
measured at a frequency of 88 Hz to 40 Kohms cm2 measured at a
frequency of 10 KHz.
23. The apparatus of claim 1, wherein the energy delivery means
provides a controlled delivery of energy to operate in a range of
thermal conductivity at a skin surface of 0.21 to 0.60 k.
24. The apparatus of claim 1, wherein the energy delivery device
provides a controlled delivery of energy to operate in a range of
compression force applied to the soft tissue structure not
exceeding 400 mmHg.
25. The apparatus of claim 1, wherein the energy delivery device
provides a controlled delivery of energy to operate in a range of
compression force applied to the soft tissue structure not
exceeding 300 mmHg.
26. The apparatus of claim 1, wherein the energy delivery device
provides a controlled delivery of energy to operate in a range of
compression force applied to the soft tissue structure not
exceeding 200 mmHg.
27. The apparatus of claim 1, wherein the energy delivery device
provides a controlled delivery of energy to operate in a range of
compression force applied to the soft tissue structure not
exceeding 100 mmHg.
28. An apparatus for modifying a skin surface or a soft tissue
structure underlying a skin surface, comprising: a template with a
non-conforming skin interface surface that applies an mechanical
force through the skin surface; a hydration delivery device coupled
to the non-conforming skin interface surface and configured to
deliver a hydration agent to the skin surface; and an energy
delivery device coupled to the non-conforming skin interface
surface and provide a controlled delivery of energy to the skin
surface.
29. The apparatus of claim 28 further comprising: a hydration
sensor coupled to the non-conforming skin interface surface.
30. The apparatus of claim 28, wherein the hydration delivery
device includes a hydraulic pressure source.
31. The apparatus of claim 30, wherein the hydration pressure
source is a mechanical source.
32. The apparatus of claim 30, wherein the hydration pressure
source is an electrical source.
33. The apparatus of claim 30, wherein the hydration pressure
source is a thermal source.
34. The apparatus of claim 30, wherein the hydration pressure
source is a chemical source.
35. The apparatus of claim 30, wherein the hydration pressure
source is ethylene glycol.
36. The apparatus of claim 30, wherein the hydration pressure
source is a diffusion gradient.
37. The apparatus of claim 30, wherein the hydration pressure
source is a compression source.
38. The apparatus of claim 28, wherein the template applies a
mechanical force to the soft tissue structure.
39. The apparatus of claim 28, further comprising: a feedback
control device coupled to the template.
40. The apparatus of claim 28, further comprising: a surface
pressure sensor coupled to the template.
41. The apparatus of claim 28, further comprising: a hydraulic
pressure sensor coupled to the template.
42. The apparatus of claim 28, further comprising: an impedance
sensor coupled to the template.
43. The apparatus of claim 28, further comprising: a surface
temperature sensor coupled to the template.
44. The apparatus of claim 28, wherein the energy delivery device
provides a controlled delivery of energy to the skin surface not
exceeding 1000 joules/cm2 during a single treatment session.
45. The apparatus of claim 28, wherein the energy delivery device
provides a controlled delivery of energy to the skin surface not
exceeding 600 joules/cm2 during a single treatment session.
46. The apparatus of claim 28, wherein the energy delivery device
provides a controlled delivery of energy to the skin surface not
exceeding 200 joules/cm2 during a single treatment session.
47. The apparatus of claim 28, wherein the energy delivery device
provides a controlled dose rate of energy to the skin surface not
exceeding 6 joules/sec/cm2.
48. The apparatus of claim 28, wherein the energy delivery device
provides a controlled dose rate energy to the skin surface not
exceeding 2 joules/sec/cm2.
49. The apparatus of claim 28, wherein the energy delivery device
provides a controlled delivery of energy to a skin surface to
operate in an impedance range at the skin surface of 70 ohms cm2
measured at a frequency of 88 Hz to 40 Kohms cm2 measured at a
frequency of 10 KHz.
50. The apparatus of claim 28, wherein the energy delivery me ans
provides a controlled delivery of energy to operate in a range of
thermal conductivity at a skin surface of 0.21 to 0.60 k.
51. The apparatus of claim 28, wherein the energy delivery device
provides a controlled delivery of energy to operate in a range of
compression force applied to the soft tissue structure not
exceeding 400 mmHg.
52. The apparatus of claim 28, wherein the energy delivery device
provides a controlled delivery of energy to operate in a range of
compression force applied to the soft tissue structure not
exceeding 300 mmHg.
53. The apparatus of claim 28, wherein the energy delivery device
provides a controlled delivery of energy to operate in a range of
compression force applied to the soft tissue structure not
exceeding 200 mmHg.
54. The apparatus of claim 28, wherein the energy delivery device
provides a controlled delivery of energy to operate in a range of
compression force applied to the soft tissue structure not
exceeding 100 mmHg.
55. A method for tightening a surface of a skin with an underlying
collagen containing tissue, comprising: providing an energy
delivery device with an energy delivery surface coupled to a
hydration delivery member; positioning the energy delivery surface
on a surface of the skin; hydrating the surface of the skin;
creating a reverse thermal gradient through the surface of the skin
to sufficient heat an underlying collagen containing tissue,
wherein a temperature of the surface of the skin is lower than a
temperature of the underlying collagen containing tissue; and
tightening at least a portion of the surface of the skin.
56. The method of claim 55, wherein the underlying collagen
containing tissue is adjacent to a hair follicle.
57. The method of claim 56, wherein at least a portion of the
underlying collagen containing tissue is ablated.
58. The method of claim 56, wherein application of the reverse
thermal gradient creates an intracellular suppression of melanin in
the hair follicle.
59. The method of claim 55, wherein the underlying collagen
containing tissue is adjacent to a sebaceous gland.
60. The method of claim 59, wherein application of the reverse
thermal at least partially modifies an oil production function of
the sebaceous gland.
61. The method of claim 55, wherein the underlying collagen
containing tissue is adjacent to a sweat gland.
62. The method of claim 61, wherein application of the reverse
thermal gradient at least partially modifies a production of sweat
from the sweat gland.
63. A method for tightening a surface of a skin with an underlying
collagen containing tissue, comprising: providing an energy
delivery device with an energy delivery surface coupled to a
hydration delivery member; positioning the energy delivery surface
on a surface of the skin; hydrating the surface of the skin with a
hydration agent; creating a reverse impedance gradient through the
surface of the skin to heat an underlying collagen containing
tissue, wherein an ECF of a post-hydrated surface of the skin is
higher than an ECF of a pre-hydrated state of the surface of the
skin; and tightening at least a portion of the surface of the
skin.
64. The method of claim 63, wherein the ECF of the post-hydrated
surface of the skin is higher than an ECF of the underlying
collagen containing tissue.
65. The method of claim 63, wherein the ECF of the post-hydrated
surface of the skin is increased and an ECF of the underlying
dermis is lowered.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] This application is a continuation-in-part of U.S. Ser. No.
08/827,237, filed Mar. 28, 1997, which is a continuation-in-part of
U.S. patent application Ser. No. 08/583,815, filed Jan. 5, 1996,
which is a continuation-in-part of U.S. patent application Ser. No.
08/435,822, filed May 5, 1995. This application also claims the
benefit of divisional applications U.S. Ser. No. 08/825,445, filed
Mar. 28, 1997 and Ser. No. 08/825,443, filed Mar. 28, 1997, and is
also related to Provisional Application Serial No. 60/023,377,
filed Aug. 6, 1996.
BACKGROUND OF THE INVENTION
[0002] 1. Field of the Invention
[0003] This invention relates to a method and apparatus for
modifying a soft tissue structure underlying a skin surface, and
more particularly to a method and apparatus which applies a
mechanical force and electromagnetic energy to the soft tissue
structure.
[0004] 2. Description of Related Art
[0005] The correction of a deformity or the esthetic enhancement of
a soft tissue structure is determined by the balance of the skin
envelope as the container and soft tissue volume as the contents of
the container. An appropriate balance between these two components
is essential in achieving a successful outcome. Most plastic
surgery procedures are based upon the resection or addition of a
soft tissue filler with a concomitant modification of the skin
envelope. For example, a breast that has three dimensional symmetry
with the opposite breast must take into account both the volume of
the soft tissue and the surface area of the breast envelope that is
required as a container of the tissue. Breast reconstruction after
mastectomy typically involves the insertion of a soft tissue
replacement for the removed breast tissue. Either an implant or a
tissue flap from the patient is used as a soft tissue replacement.
Expansion of the breast skin envelope is also required and is
achieved with a medical device called a breast expander. While most
reconstructive procedures usually involve the addition of a soft
tissue filler with the expansion of the skin envelope, many
esthetic procedures involve the reduction of the soft tissue
contents with or without a reduction in the skin envelope.
Reduction in the volume of the soft tissue contents without a
concomitant reduction in the skin envelope may lead to a relative
excess of the skin envelope. The relative excess will be visualized
as loose skin or elastosis. An example of esthetic enhancement is a
procedure called breast reduction. This is performed in women who
require reduction in the size of their breasts to alleviate
shoulder, neck and back symptoms. Breast tissue is resected to
reduce volume but also requires a reduction in the breast skin
envelope with extensive surgical incisions. Without reduction of
the skin envelope of the breast, severe ptosis (droopiness) of the
breast will occur.
[0006] Another example is liposuction which may aggravate elastosis
because the soft tissue content is reduced without reduction in the
surface area of the skin envelope. The degree of esthetic contour
reduction is limited by the preexisting looseness of the skin
envelope. Typically, liposuction involves the removal of
subcutaneous fat through a suction cannula inserted through the
skin surface. Excess suctioning of fat will aggravate any
preexisting elastosis. Any other modality that reduces subcutaneous
fat through dieting or ablation of fat cells is likely to aggravate
a preexisting elastosis if a concomitant reduction of the skin
envelope does not occur. This is especially true in the hip and
thigh area where a condition called "cellulite" is due to a
preexisting looseness of skin. Many patients have a more severe
looseness of skin in the hip and thigh area that would be
aggravated by any fat removal. Skin tightening procedures that
involve large surgical incisions result in severe scarring to the
thigh and hip area that are a poor tradeoff to any esthetic contour
reduction.
[0007] There is a need for a method and apparatus to achieve skin
tightening without major surgical intervention. There is a further
need for a method and apparatus to achieve skin tightening by the
controlled remodeling of collagen in the skin and underlying
fibrous partitions of the subcutaneous fat. Still a further need
exists to tighten a skin envelop with minimal skin or underlying
subcutaneous tissue cell necrosis. Yet another need exists to
provide a method and apparatus for the controlled remodeling of
collagen in tandem with subcutaneous fat ablation in which a net
tightening of the skin envelope occurs with an esthetic contour
reduction.
SUMMARY OF THE INVENTION
[0008] Accordingly, an object of the invention is to provide a
method and apparatus to tighten skin.
[0009] Another object of the invention is to provide a method and
apparatus for creating a reverse thermal gradient through a skin
surface.
[0010] Yet another object of the invention is to provide a method
and apparatus for creating a reverse impedance gradient from the
skin surface to underlying tissue.
[0011] Still another object of the invention is to provide a method
and apparatus for hydrating the skin.
[0012] Another object of the invention is to provide a method and
apparatus for creating a reverse thermal gradient from the skin to
underlying tissue, with the creation of an ablation in the
underlying tissue.
[0013] Yet another object of the invention is to provide a method
and apparatus that creates an intracellular suppression of a tissue
site underlying the skin surface.
[0014] A further object of the invention is to provide a method and
apparatus that modifies a physiological function of a tissue site
underlying the skin.
[0015] These and other objects of the invention are achieved in an
apparatus for modifying a skin surface or a soft tissue structure
underlying a skin surface. The apparatus includes a skin surface
conforming member and a hydration delivery device coupled to the
conforming member. The hydration delivery device delivers a
hydration agent to the skin surface. An energy delivery device is
coupled to the conforming member and provides a controlled delivery
of energy to the skin surface.
[0016] In one embodiment of the present invention, an apparatus for
modifying a skin surface or a soft tissue structure underlying a
skin surface includes a template positionable adjacent to the skin
surface to apply a mechanical force through the skin surface. A
hydration delivery device is coupled to the conforming member and
delivers a hydration agent to the skin surface. An energy delivery
device is coupled to the conforming template and provides a
controlled delivery of energy to the skin surface.
[0017] In another embodiment, a method produces a tightening of a
surface of a skin with an underlying collagen containing tissue. An
energy delivery device is provided with an energy delivery surface
coupled to a hydration delivery member.
[0018] The energy delivery surface on a surface of the skin and the
surface of the skin is hydrated. A reverse thermal is created
through the surface of the skin to heat an underlying collagen
containing tissue. The temperature of the surface of the skin is
lower than a temperature of the underlying collagen containing
tissue and at least a portion of the surface of the skin is
tightened.
[0019] In another embodiment of the invention is a method that
tightens a surface of the skin. An energy delivery device is
provided with an energy delivery surface coupled to a hydration
delivery member. The energy delivery surface is positioned on a
surface of the skin and the skin surface is hydrated. A reverse
impedance gradient is formed through the skin surface to an
underlying collagen containing tissue. An ECF of the surface layers
of the skin, stratum corneum, epidermis, and superficial dermis of
the skin, is increased and ECF of the underlying collagen
containing tissue is decreased in comparison to the pre-hydration
state. At least a portion of the skin surface is tightened.
BRIEF DESCRIPTION OF THE FIGURES
[0020] FIG. 1 is a cross-sectional view of a template of the
present invention.
[0021] FIG. 2 is a lateral section view of the template illustrated
in FIG. 1.
[0022] FIG. 3 is an illustration of an iontophoretic hydration
device coupled to a template of FIG. 1.
[0023] FIG. 4 is an illustration of a hydraulic hydration device
coupled to a template of FIG. 1.
[0024] FIG. 5 is a cut-away view of a skin surface with a hydrating
template of FIG. 4 acting to hydrate the skin and subcutaneous
layers.
[0025] FIG. 6 is a cut-away view of a skin surface and underlying
tissue illustrating the ablation or altering of function of skin
appendages.
[0026] FIG. 7 is an illustration of the secondary effects of
collagen remodeling on skin appendages.
[0027] FIG. 8 is an illustration of ablation of a hair follicle as
a result of collagen remodeling.
[0028] FIG. 9 is an illustration of an intracellular modification
of a hair follicle resulting from collagen remodeling.
[0029] FIG. 10 is an illustration of hair growth in a hair follicle
caused by intracellular modification from collagen remodeling.
[0030] FIG. 11 is a cut-away view of a skin surface that is being
subjected to hydration and electromagnetic radiation, and
illustrating the effect of hydration on impedance.
[0031] FIG. 12 illustrates intramolecular cross-linking of
collagen.
[0032] FIG. 13 illustrates intermolecular cross-linking of
collagen.
[0033] FIGS. 14 and 15 are two graphs illustrating a probability of
collagen cleavage with changing bond strength at 37 degrees C.
[0034] FIG. 16 is a top down view of a skin surface, illustrating
the peaks and valleys of the surface and the vectors applied to the
surface by the application of a mechanical force.
[0035] FIG. 17 is a cross-sectional view of the skin surface
illustrated in FIG. 16.
[0036] FIG. 18 is a cut-away view of the skin surface, with troughs
and ridges, and underlying subcutaneous soft tissue.
[0037] FIG. 19(a) is a lateral perspective view of a telescoping
segment of a breast expander useful with the apparatus of FIG.
1.
[0038] FIG. 19(b) is a front perspective view of the breast
expander of FIG. 19(a).
[0039] FIG. 19(c) illustrates a bra which functions as the template
of FIG. 1.
[0040] FIG. 19(d) is a lateral cross-sectional perspective view of
a partially expanded breast expander within a breast.
[0041] FIG. 19(e) is a lateral cross-sectional perspective view of
a fully expanded breast expander within a breast.
[0042] FIG. 20 illustrates a template in the form of a garment.
[0043] FIG. 21(a) illustrates a template that is positioned over a
nose.
[0044] FIG. 21(b) illustrates a template that is positioned over an
ear.
[0045] FIG. 22 is a perspective view of a template that is useful
in the cervix.
[0046] FIG. 23 is a cross-sectional view of the template of FIG.
22.
[0047] FIG. 24(a) is a front view of an orthodontic appliance that
includes RF electrodes.
[0048] FIG. 24(b) is perspective view of an orthodontic appliance
template of the device of FIG. 1.
[0049] FIG. 24(c) is cross-sectional view of the template of FIG.
24(b)
[0050] FIG. 25 illustrates a template made of a semisolid material
that becomes more conforming to underlying soft tissue upon the
application of a mechanical force.
[0051] FIG. 26 illustrates a template with an adherent or suction
mechanical force delivery surface that permits manual manipulation
of skin and soft tissue structures.
[0052] FIG. 27 is a schematic diagram of an analog embodiment of
the controller for use in the apparatus of FIG. 1.
[0053] FIGS. 28 through 31 represent a schematic block diagram of a
microprocessor controlled impedance monitoring apparatus for
controlling RF energy delivered by the apparatus of FIG. 1.
DETAILED DESCRIPTION
[0054] Referring now to FIGS. 1 and 2, an apparatus 10 modifies a
skin surface or a soft tissue structure underlying the skin
surface. A template 12 includes a soft tissue mechanical force
application surface 14 and a receiving opening 16 to receive a body
structure. Mechanical force application surface 14 is configured to
receive the body structure and apply pressure to soft tissue in the
body structure. An energy delivery device 18 is coupled to template
12. Energy delivery device 18 is configured to deliver sufficient
energy to template 12 to form a template energy delivery surface 20
at an interior of template 12.
[0055] Mechanical force application surface 14 can apply pressure,
suction, adhesion and the like in order to create an extension or
compression of the soft tissue collagen containing structure and/or
the skin surface.
[0056] Energy delivery device 18 and an energy source may be a
single unit or each can be separate. Suitable energy sources 22
include but are not limited to the following: resistive heating,
RF, coherent and incoherent light, microwave, electrical, thermal,
magnetic, frictional heating, ultrasound, liquid thermal jet and
cryogenic fluid energy sources. Energy delivery device 18 can form
an energy delivery surface 20 in template 12 which can be the same
size as mechanical force application surface 14.
[0057] Template 12 applies both a mechanical force and delivers
energy to, (i) tighten the skin, (ii) smooth the surface of the
skin, (iii) improve a compliance of the skin surface, (iv) improve
a flexibility of the skin surface and (v) provide cellular
remodeling of collagen in soft tissue anatomical structures.
Mechanical force application surface 14, (i) is at least partially
conforming to the skin surface, (ii) may apply a substantially even
pressure to the soft tissue anatomical structures and (iii) can
apply a variable pressure to the skin surface and underlying soft
tissue structures. The combined delivery of electromagnetic energy
and a mechanical force is used to create a three-dimensional
contouring of the soft tissue structure. The amount of mechanical
force applied by mechanical force application surface 14, (i) is
sufficient to achieve a smoothing effect of the skin surface, (ii)
can be less than the tensile strength of collagen in tissue and
(iii) is sufficient to create vectors that cleave collagen
cross-links to remodel collagen containing structures.
[0058] FIG. 3 illustrates apparatus 10 with an iontophoretic
hydration device coupled to a template 12 in order to hydrate the
target skin. Hydration of the skin is provided to convection cool
and hydrate through a conductive semipermeability mobile membrane
13 of template 12 at surface 14. The hydration can be achieved with
the delivery of a hydration medium from a reservoir 11 through the
pores 15 of the membrane 13. The reservoir 11 can be coupled or
de-coupled from template 12 by attaching or removing the reservoir
connection tube 17. Permeability of the conductive semipermeability
mobile membrane 13 can be altered by the development of an
electrostatic or dielectric charge. Membrane permeability can also
be altered by mechanically altering the thickness of the membrane,
with or without tension. A change in membrane temperature also
alters the permeability.
[0059] FIG. 4 illustrates another embodiment of apparatus 10 in
which a hydraulic hydration device is coupled to a template 12 to
hydrate the target skin. In this embodiment, hydraulic pressure can
be used to vary the hydration rate. A hydraulic pressure gradient
is produced and can be controlled by a feedback control system 28.
The feedback control system 28 can receive inputs from a surface
feedback sensor 21 that measures temperature or impedance, and/or a
pressure sensor 25.
[0060] The semiporous membrane 13 dilates with the creation of a
hydraulic pressure gradient. The hydraulic pressure applied can be
no more than 300 mm Hg. The semiporous membrane 13 becomes more
porous as the chamber 19 is inflated with hydrating solution, and
as the membrane conforms to the skin in a repeating peak
configuration. In this configuration, the porosity of the membrane
13 increases when hydraulic pressure in the chamber 19 increases.
Hydraulic pressure is increased/maintained in the chamber 19
through the operation of the hydraulic pump 31 which is installed
in series with the reservoir 11 and the chamber 19. The hydrating
fluid is drawn from the reservoir 11 by the suction of the
hydraulic pump 31 and the fluid is drawn through the reservoir
connection tube 17 and enters the chamber 19 via the instillation
channel 33.
[0061] The pressure in the chamber is variable and can be coupled
to the feedback control system 28. The hydraulic damper 29, in
conjunction with the collection bag 27 serves to increase or
decrease the pressure in the chamber 19 by increasing or decreasing
the restriction of hydrating fluid flow in accordance with signals
supplied by the feedback control system 28. For instance, surface
impedance measures the level of hydration. If the impedance is too
low then the feedback control system 28 can act to either open
damper 29 fully to decrease chamber 19 pressure and thus cease
hydration, or convert to convection cooling. If the impedance is
too high then a hydraulic pressure gradient can be produced to
increase hydration by shutting damper 29.
[0062] A hydraulic hydration device may be incorporated with the
remodeling apparatus 10 as shown in FIG. 4, or it may be used
separately. It may also be used concurrently with remodeling
apparatus 10 for surface convection cooling. The repeating peak
configuration of the membrane 13 that is formed with the creation
of a hydraulic gradient more effectively instills a sterile saline
solution (or sterile water) with transcutaneous hydration. Each
peak becomes more porous and represents an installation port.
During hydration, hydraulic pressure is achieved by the cessation
of flow due to the closing of damper 29, although the hydraulic
pump 31 continues to function. Hydraulic pressure is modulated by a
pressure sensor 25 instead of a flow sensor. However, a hydration
sequence is initiated with an impedance backed sensor 21.
[0063] When hydration and remodeling are performed using separate
devices, the surface 14 of the apparatus 10 can be smooth and
non-porous. The membrane 13 of the hydration device must be
prefabricated with the desired uniform peak configuration such that
it becomes more porous with increasing hydraulic pressure. The
hydraulic pressure gradient is created with a hydraulic pump 31
attached in series to a sterile solution. The gradient created may
be continuous or pulsatile. This hydraulic/hydration device can
also be used for the transcutaneous infusion of local anesthesia
and/or medication.
[0064] As discussed, the hydraulic hydration device may be
incorporated with the remodeling apparatus 10 for hydration and can
also be used concurrently for convection surface cooling. The
feedback control system 28 can utilize a flow damper algorithm to
adjust the position of the damper 29 to regulate convection cooling
based on surface 14 temperature and/or impedance. The temperature
and/or impedance can be provided by a surface sensor 21. During
hydration the damper 29 is closed and fluid flow ceases. For
convection cooling, the damper 29 is open. In this manner, the
device can provide a flow rate of a sterile solution for surface
convection cooling that is modulated by a feedback surface
temperature or impedance sensor 21.
[0065] As illustrated in FIG. 5, hydration is applied through the
exterior of the skin and to selected areas of the skin.
Additionally, the hydration medium can be delivered through the
skin to collagen containing tissue. Hydration can be applied
continuously, non-continuously, at one steady rate or at varied
rates.
[0066] Hydration is monitored by impedance feedback, as more fully
explained hereafter. RF energy delivery does not occur unless the
surface impedance has dropped below a level that will not ablate or
blister the skin surface. Initially, delivery of low level RF
energy is performed to promote hydration and transcutaneous
permeation of a local anesthetic. This is similar to an
iontophoretic device. Following the achievement of anesthesia with
a desired surface impedance, the treatment phase begins with the
delivery of energy at a dose and dose rate that achieves
contraction and remodeling of the matrix. In one embodiment, RF
electrodes are used for the dual purpose of iontophoresis and
collagen remodeling. Overall, apparatus 10 has multiple functions
that are coupled with feedback control in a single geometry, i.e.,
energy delivery, conformance, convection cooling, hydration and
topical anesthetic delivery. In another embodiment, separate
devices with similar surface geometry are used for hydration and
matrix remodeling.
[0067] Other than collagen remodeling, the application of a reverse
thermal gradient with a conforming electromagnetic device can
either ablate or alter the function of skin appendages such as hair
follicles or sebaceous glands. Non-invasive hair removal through
the ablation of the hair follicle is possible with a conforming
electromagnetic device. This use is illustrated in FIG. 6. Dose and
dose rate parameters of thermal energy, such as RF, are identified
that will achieve hair removal while minimizing blistering of the
skin surface. For this application, a deeper level of hydration is
required as the base of the hair follicle (germinal epithelium) is
sub-dermal. Injection of an impedance enhancing solution, such as
glucose, into the follicle improves thermal release at the target
structure. A higher dose rate with a small overall dose to the
target and adjacent tissues is used for ablation of the hair
follicle. A large energy dose to a small area of the hair follicle
is delivered in a short period of time to minimize collateral
damage to adjacent tissues.
[0068] Excessive sebum formation by the sebaceous gland is the
major cause of an oily complexion. Excessive sebum formation may
also be a precursor to acne vulgaris. A non-invasive reduction in
sebum formation benefits patients with acne vulgaris. Medications,
such as Acutane, have had partial success in reducing sebum
formation but may have significant long term side effects,
especially for young women during child bearing years.
[0069] As the sebaceous gland is intradermal, a reduction in the
size of the structure can be achieved by contraction of the
adjacent collagen matrix. Additionally, a partial ablation or
intracellular suppression of sebum formation can be achieved with
an energy delivery profile that is similar to that used in hair
follicle ablation, i.e., high dose rate over short periods of time.
A more superficial level of hydration is required as the sebaceous
gland is located within the dermis. This is also illustrated in
FIG. 6.
[0070] An additional clinical application is the ablation or
intra-cellular modification of the sweat gland. The eccrine sweat
gland has a thermal/regulatory function to maintain temperature
homeostasis. The apocrine sweat gland is present in the axilla and
perineal regions and is responsible for body odor. In addition, a
disease condition of the apocrine sweat gland, hidradenitis
suprativa, can result in the recurrent infection of the axillary
and perineal regions. Suppression of the apocrine sweat gland will
reduce body odor and may prevent either the development or
recurrence of infections in the axillae and perineal regions.
Excessive eccrine sweating may also be avoided especially in women
with "hot flashes". The subdermal and deeper dermal layers is the
treatment zone for modification of sweating. This is achieved with
a partial ablation of the apocrine sweat gland, in conjunction with
a contraction of a sufficient amount of collagen containing tissue
surrounding the apocrine sweat gland. Collagen contraction inhibits
the physiology function of the apocrine sweat gland. This
application is also illustrated in FIG. 6.
[0071] The application of a reverse thermal gradient with a
conforming electromagnetic device can also be used for the
treatment of dermal micro varicosities in a non-invasive manner.
Hydration levels and dose rate/dose profiles are similar to the
treatment of the overactive sebaceous gland. The contraction of the
adjacent matrix around the micro varicosity diminishes the diameter
of the structure. Non-invasive ablation of the varix is also
possible with the manipulation of impedance with hydration and the
selection of the appropriate dose rate/dose profile. This
application is also illustrated in FIG. 6.
[0072] When the apparatus 10 is used for the primary purpose of
contracting the collagen structure of a skin area there are
corresponding secondary effects on skin appendages such as hair
follicles, sebaceous glands, sweat glands, and dermal and subdermal
capillaries for microvaricosity.
[0073] For instance, without ablation of the hair follicle, it may
be possible to change the morphology of the hair from curly to
straight and vice-versa. Hair color can also be modified in this
manner with a reduction of melanin pigment produced in the hair
follicle. This is achieved by intracellular modification of
physiological function by contracting underlying collagen
containing tissue surrounding the hair follicles. However, there is
a direct effect of the electromagnetic energy with either ablation
or intracellular modification in that it changes the physiological
function of the skin appendages. This is illustrated in FIGS. 7, 8,
9, and 10.
[0074] Restoration of hair growth represents another important
application that can be induced by electromagnetic radiation. Solar
radiation has naturally modified intracellular function of skin
over the millennia. The body's production of melanin by melanocytes
to preserve hair and induce hair growth has responded to a specific
frequency of the electromagnetic spectrum in the ultraviolet range.
Thus, as solar radiation has modulated intracellular function over
time, the damage has been mitigated by a physiological
reaction.
[0075] In contrast, Keratin production in the skin by keratinocytes
is less responsive to electromagnetic radiation than to
mechanically applied energy. Frictional forces applied to the skin
surface typically stimulate keratinocytic function. Callus
formation is the morphological expression of this stimulation.
[0076] The hair follicle is comprised of melanocytes and
keratinocytes in the germinal epithelium. The potential exists that
the combination of mechanical force will incite keratin stimulation
and that a specific frequency of electromagnetic radiation will
induce pigment production. The net result is the growth of hair
with a specific pigmentary pattern. Modern day medical devices that
create specific vibrational frequencies can be coupled with
electromagnetic sources that induce hair growth with a selected
pigmentation.
[0077] In this application, delivery of electromagnetic radiation
without surface ablation is facilitated with hydration. However,
percolation without surface absorption of an impedance enhancing
solution such as glucose into the hair follicle will direct the RF
energy to this target skin appendage. For optical sources of
energy, percolation of a nonabsorbent photodynamic dye into the
hair follicle should provide similar benefits for ablation or
modification of hair growth or hair color.
[0078] Referring back to FIG. 1, a sensor 21 is positioned at
template energy delivery surface to monitor temperature, impedance
and the like. Suitable sensors 21 include impedance and thermal
devices. Sensor 21 is used to control the delivery of energy and
reduce the chance of cell necrosis at the surface of the skin as
well as damage to underlying soft tissue structures. Sensor 21 can
also be used to provide input to the feedback control system 28 of
a hydraulic hydration device. Sensor 21 is of conventional design,
including but not limited to thermistors, thermocouples, resistive
wires, and the like. A suitable thermal sensor 21 includes a T type
thermocouple with copper constantene, J type, E type, K type, fiber
optics, resistive wires, thermocouple IR detectors, and the
like.
[0079] For most transcutaneous applications, the transmission of
energy through the skin surface may function as a series impedance
system. Increasing the extra-cellular fluid with hydration will
decrease surface impedance and facilitate energy transfer through
the skin without surface ablation. Subjacent non-hydrated dermal
matrix will have a comparably higher impedance which is selectively
heated and remodeled. This is illustrated in FIG. 11.
[0080] Hydration can be achieved with either extrinsic or intrinsic
approaches. Extrinsic hydration is provided with either
iontophoretic or hydraulic means. In addition to the reduction of
surface impedance, extrinsic hydration provides the means to
deliver medications, lotions or photodynamic dyes into the dermis.
Installation of an optical dye into the dermis with a similar
absorption spectrum of the incident optical source allows delivery
of energy into the dermal collagen while reducing surface
absorption. Accordingly, the peak absorption spectrum of the dye
should be different than the absorption spectrum of the epidermis
or the stratum corneum. The hydraulic device may have a conforming
surface to provide a more uniform pattern of hydration.
[0081] Intrinsic hydration is achieved with either a conforming or
non-conforming surface that is non-permeable or occlusive. A
thermal energy source is coupled to and, and in one embodiment is
incorporated in, the occlusive surface to facilitate hydration of
the stratum corneum from the dermal ECF in a retrograde fashion. A
reverse impedance gradient is created between the stratum corneum
and the dermis, i.e., ECF content is raised in the stratum corneum
and is lowered in the dermis. Surface impedance is measured and
used as a feedback control device to determine an adequate amount
of hydration to avoid surface ablation. The conforming intrinsic
hydration device with a thermal energy source, including but not
limited to RF, may not have a different end stage geometry than the
treatment device in which hydration and collagen remodeling occurs
concurrently. Intrinsic hydration also facilitates topical
diffusion of medication, lotions, photodynamic therapy dyes,
pharmacologic agents and the like.
[0082] Apparatus 10 is designed for the specific energy
requirements of each type of bond within the collagen matrix.
Collagen crosslinks may be either intramolecular (hydrogen bond) or
intermolecular (covalent and ionic bonds). Hydrogen bonds are
disrupted by heat. Covalent bonds may be cleaved with the stress
created from the hydrogen bond disruption and the application of an
external mechanical force. Cleavage of ionic bonds may be achieved
with an alternating electrical moment in addition to the
application of an external mechanical force that is applied by
template 12. The strength of a hydrogen bond is relatively weak and
can be thermally disrupted without ablation of tissue. The in vitro
thermal cleavage of the hydrogen bond crosslinks of tropocollagen
can result in the molecular contraction of the triple helix up to
one third of its original length. However, in vivo collagen exists
in fibrils that have extensive intermolecular crosslinks that are
covalent or ionic. These covalent and ionic crosslinks are stronger
and cannot be easily disrupted with heat. These intermolecular
bonds are the main structural determinants of matrix strength and
morphology. In vivo thermal disruption of intramolecular hydrogen
bonds will not by itself result in a significant change in matrix
morphology. As the intermolecular crosslinks are heat stable,
cleavage may occur by a secondary mechanical process which can be
the result of thermal disruption of intramolecular hydrogen bonds.
In the non-polar region of the collagen fibril, intermolecular
covalent bonds predominate (intramolecular covalent bonds are also
present but are fewer in number).
[0083] These intermolecular covalent crosslinks increase with age,
see FIGS. 12 and 13. As a result, the solubility of the collagen
matrix in a soft tissue structure is reduced with this maturation
process. Although tensile strength is increased, the collagen
containing tissue becomes less compliant. Cleavage of an
intermolecular bond requires approximately 1 ev of energy and can
not be accomplished by heat without thermal ablation of tissue. In
addition, covalent bonds are not strongly polar and will not be
significantly affected by an RF current at this reduced power
level. Cleavage of intermolecular covalent bonds that result in
matrix remodeling without ablation is achieved by the stress
created from the thermal disruption of intramolecular hydrogen
bonds. Additional remodeling stress can be provided with the
application of an external force that has the appropriate
orientation to the fibrils of the matrix. Ionic bonds are
essentially intermolecular and are present in the polar regions of
the fibril. Although slightly weaker than covalent bonds, thermal
disruption cannot occur without ablation of tissue. An RF field is
an effective means to cleave these bonds and is created by an in
phase alternating ionic motion of the extracellular fluid.
Frequency modulation of the RF current may allow coupling to the
ionic bonds in the polar regions of the fibril. Remodeling of a
target site may be optimized by the selection of a band of the
spectrum that is target site specific in order to reduce collateral
damage. If an optimized intrinsic absorption is insufficient then a
selective medium may be provided to alter the absorption in order
to discriminate various soft tissue structures. This may be
achieved by altering the absorption. By altering the extra-cellular
fluid content of a soft tissue in specific ways, the delivery of
energy to a target tissue site is achieved with minimal damage to
collateral structures such as skin and adjacent soft tissue
structures.
[0084] The reforming of bonds at the same bond sites will diminish
the remodeling process. Relaxation phenomena may be inhibited with
the application of an external mechanical force that separates bond
sites but allows the reforming of these covalent and ionic bonds in
a lengthened or contracted morphology. This can be the underlying
biophysical process that occurs with the controlled remodeling of
the collagen matrix. Ground substance may also function to diminish
relaxation of crosslinks through competitive inhibition.
Chondroitin sulfate is a highly charged molecule that is attached
to a protein in a "bottle brush" configuration. This configuration
promotes attachment at polar regions of the fibril and reduces the
relaxation of ionic bonds in this region. As a consequence,
immature soluble collagen, which has fewer intermolecular
crosslinks and contains a higher concentration of ground substance,
may be more easily remodeled. The induction of scar collagen
through the wound healing sequence may also facilitate the
remodeling process within a treatment area.
[0085] The cleavage of a collagen crosslink requires an energy
threshold. However, collagen cleavage in tissue is a probability
event. There is a greater probability that a collagen bond will be
cleaved with higher temperatures. Cleavage of collagen bonds will
occur at lower temperatures but at a lower frequency. Low level
thermal cleavage is frequently associated with relaxation phenomena
in which there is not a net change in molecular length. An external
force that mechanically cleaves the fibril may reduce the
probability of relaxation phenomena. The application of an external
force will also provide a means to lengthen or contract the
collagen matrix at lower temperatures while reducing the potential
of surface ablation. The cleavage of crosslinks with collagen
remodeling may be occurring at a basal metabolic temperature that
is expressed morphologically as the process of aging. Although the
probability for significant cleavage in a short period of time is
small, aging may be expressed as a low level steady state of
collagen remodeling with the external force of gravity that becomes
very significant over a period of decades.
[0086] Hydrogen bonds which are relatively weak (0.2 ev to 0.4 ev)
are formed within the tertiary structure of the tropocollagen
molecule. Thermal disruption of these bonds can be achieved without
ablation of tissue, i.e., cell necrosis. The probability of
hydrogen bond disruption at a certain temperature can be predicted
by statistical thermodynamics. If a Boltzmann distribution is used
to calculate the probability of bond disruption then a graph
illustrating the relationship between bond strength and the
probability of bond disruption at a certain temperature can be
produced. Graphs of the probability of cleavage at 37 degrees
centigrade with various bond strengths are shown in FIGS. 14 and
15.
[0087] Different morphological expressions of aging may be due to
the effect of gravity upon the matrix of a particular area. In
areas of the skin envelope in which gravity lengthens the matrix,
elastosis of skin will occur. In contrast to skin aging, certain
anatomical structures such as joint ligaments will appear to
tighten with the aging process. The reduced range of motion may be
due in part to the vertical vector of gravity contracting the
matrix of a vertically aligned ligament. However, most of the
"tightening" or reduced range of motion of joints may not be
secondary to a contracted matrix but is due to reduced flexibility
of the matrix caused by increased intramolecular cross-linking that
occurs with aging. Essentially, the controlled remodeling of
collagen is the reversal of the aging process and involves the
reduction in the number of intermolecular crosslinks. As a result
the remodeled matrix becomes less brittle. Greater flexibility of
the soft tissue has several functional advantages including an
increased range of motion of component joints.
[0088] When the rate of thermal cleavage of intramolecular
crosslinks exceeds the rate of relaxation (reforming of hydrogen
bonds) then the contraction of the tertiary structure of the
molecule can be achieved. No external force is required for this
process to occur. Essentially, the contraction of the tertiary
structure of the molecule creates the initial intermolecular vector
of contraction. The application of an external mechanical force
during thermal cleavage will also affect the length of the collagen
fibril and is determined by the overall sum of intrinsic and
extrinsic vectors that is applied during a cleavage event. Collagen
fibrils in a matrix exhibit a variety of spatial orientations. The
matrix is lengthened if the sum of all vectors act to distract the
fibril. Contraction of the matrix is facilitated if the sum of all
extrinsic vectors acts to shorten the fibril. Thermal disruption of
intramolecular bonds and mechanical cleavage of intermolecular
crosslinks is also affected by relaxation events that restore
preexisting configurations. However, a permanent change of
molecular length will occur if crosslinks are reformed after
lengthening or contraction of the collagen fibril. The continuous
application of an external mechanical force will increase the
probability of crosslinks forming after lengthening or contraction
of the fibril.
[0089] The amount of (intramolecular) hydrogen bond cleavage
required will be determined by the combined ionic and covalent
intermolecular bond strengths within the collagen fibril. Until
this threshold is reached little or no change in the quaternary
structure of the collagen fibril will occur. When the
intermolecular stress is adequate, cleavage of the ionic and
covalent bonds will occur. Typically, the intermolecular cleavage
of ionic and covalent bonds will occur with a ratcheting effect
from the realignment of polar and non-polar regions in the
lengthened or contracted fibril. Birefringence (as seen with the
electron microscope) of the collagen fibril may be altered but not
lost with this remodeling process. The quarter staggered
configuration of the tropocollagen molecules in the native fiber
exhibits a 680 .ANG. banding which either lengthens or contracts
depending on the clinical application.
[0090] Application of the mechanical force with template 12 during
the remodeling process determines if a lengthened or contracted
morphology of the collagen fibril is created. An external force of
contraction will result in the contraction of the tertiary and
quaternary structure of the matrix. With the application of an
external distraction force, intramolecular contraction may still
occur from the intrinsic vector that is inherent within its
tertiary structure. However, overall lengthening of the quaternary
structure of the fibril will occur due to the mechanical cleavage
of the intermolecular bonds. Contraction of the tertiary structure
with overall lengthening of the collagen fibril can alter the
birefringence of the matrix. The altered periodicity will be
exhibited in the remodeled matrix that will correlate to the amount
of lengthening achieved.
[0091] Delivery of both electromagnetic energy and mechanical
energy to the selected body structure involves both molecular and
cellular remodeling of collagen containing tissues. The use of low
level thermal treatments over several days provides an additional
way to contract skin with minimal blistering and cell necrosis.
Cellular contraction involves the initiation of an
inflammatory/wound healing sequence that is perpetuated over
several weeks with sequential and lengthy low level thermal
treatments. Contraction of skin is achieved through fibroblastic
multiplication and contraction with the deposition of a static
supporting matrix of nascent scar collagen. This cellular
contraction process is a biological threshold event initiated by
the degranulation of the mast cell that releases histamine. This
histamine release initiates the inflammatory wound healing
sequence.
[0092] Molecular contraction of collagen is a more immediate
biophysical process that occurs most efficiently with
electromagnetic energy delivery devices, including but not limited
to RF electrodes. The clinical setting is physician controlled and
requires more precise temperature, impedance, and energy delivery
monitoring to avoid blistering of the skin. Measured impedance will
vary with the frequency of the electromagnetic energy applied to
the skin surface and/or underlying soft tissue structure.
Continuous monitoring of impedance is used to measure the amount of
skin surface hydration that is required for the transcutaneous
delivery of electromagnetic energy. Monitoring of surface
temperature for water content of the skin surface is important for
thermal energy sources, i.e., when thermal conductivity is enhanced
with hydration.
[0093] Patients may be treated with one or both modalities to
achieve the optimal esthetic result. Refinements to the treatment
area may be required using apparatus 10 in the physician's
office.
[0094] However, tightening of a skin surface without application of
external compression may accentuate any preexisting contour
irregularities. For this reason, conforming esthetic template 12 is
used to smooth surface contour irregularities. Essentially, the
application of a mechanical force upon the collagen matrix involves
both contraction or distraction of the selected soft tissue
structure to achieve a smoother contour. Thermal (or em) cleavage
of collagen crosslinks when combined with a mechanical force
creates vectors that contract, distract or shear the longitudinal
axis of the fibril. A vector space is created with the combination
of a scalar component (heat) and a vector (an externally applied
mechanical force). The vectors within this vector space vary
depending upon the specific morphology. For example, the peaks and
valleys of cellulite will have different vectors when uniform
external compression is applied. As illustrated in FIGS. 16 and 17,
template 12 produces converging and diverging vectors that smooth
surface morphology by contracting (valleys) and distracting (peaks)
the collagen matrix in a soft tissue structure. Diverging vectors
on the peaks lengthen the collagen matrix while converging vectors
in the valleys contract and compact the collagen matrix. The
overall result is the smoothing of an irregular skin surface.
[0095] Apparatus 10 may also be used to treat wrinkling of the
skin. The treatment of skin wrinkles is shown in FIG. 18. In a skin
wrinkle the vectors are directed perpendicular to the troughs and
ridges of this contour deformity. Diverging vectors at the ridges
of the skin converge in the trough of the wrinkle to smooth the
surface morphology . The collagen matrix is distracted or extended
at the ridges and contracted in the valleys. The overall result is
the smoothing of the wrinkled skin surface.
[0096] Linear scars exhibit a similar morphology and can be
remodeled with apparatus 10. Any surface irregularity with
depressions and elevations will have vectors directed to the lowest
point of the deformity. Prominent "pores" or acne scaring of the
skin have a similar pattern to cellulite but on a smaller scale and
can also be treated with apparatus 10. Clinically, the application
of the mechanical force reduces the power required to remodel the
matrix and diminishes cell necrosis of the skin surface as well as
underlying soft tissue structures. Compression alters the
extracellular fluid of the soft tissue structure (collagen) and
exerts electrical impedance and thermal conductivity effects that
allow delineation of a conduit-treatment interface of the collagen
containing tissues. A deeper dermal interface will contract skin
and exert three dimensional contour effects while a more
superficial interface will smooth surface morphology.
[0097] In circumstances in which expansion of the skin envelope is
needed, the combined application of heat and pressure is also
required. For breast reconstruction, expansion of the skin envelope
is typically achieved with each inflation of a subpectoral breast
expander. FIGS. 19(a) and 19(b) illustrate an expander with an RF
receiver electrode. A telescoping segment with an RF energy source
is incorporated with access valve and is used to expand a nipple
areolar donor site for Pectoralis "Peg" Procedure. The segmental
expander can also be used to prepare the recipient site for delayed
autologous "Peg" Flap. The pressure that is exerted on the skin and
the periprosthetic scar capsule is from the inside. In this
application, vectors are directed outward. As an adjunct to this
expansion process, a controlled thermal pad may be incorporated
into a bra, as illustrated in FIG. 19(c), which can be applied to
the inferior pole of the breast skin to promote lengthening of
collagen fibril within the skin and underlying scar capsule around
the expander. The bra may also function as an external conforming
template 12 to achieve a specific breast shape. The net result is
the creation of a more esthetic breast reconstruction with three
dimensional characteristics of the opposite breast. In a like
manner, other garments with incorporated thermal energy sources can
be utilized as external conforming templates for other anatomical
body structures.
[0098] In FIG. 19(d) a breast expander is partially expanded within
the breast. In FIG. 19(e), the expander is fully expanded within
the breast.
[0099] Template 12 applies a mechanical force in combination with
the delivery of energy, with minimal cell necrosis to the skin
surface and underlying soft tissue structure, to remodel collagen
both esthetically and functionally. Template 12 can be in a variety
of different forms including but not limited to a garment that is
illustrated in FIG. 20. Energy source 22 can be directly
incorporated into the fabric of a tight fitting garment or inserted
as a heating/RF pad into a pocket of the garment. Another example
of a garment is a tight fitting bra that extends over the arm and
waistline with zone control that provides contraction of the skin
of the breast, arms, and waistline to a variable amount to create a
desired three-dimensional figure. Functional remodeling of collagen
containing structures include a variety of different applications
for aesthetic remodeling.
[0100] As shown in FIGS. 21(a) and 21(b), template 12 can be a
garment positioned over the nose, a garment positioned around the
ear, and the like.
[0101] Template 12 can also be applied for functional purposes.
Referring now to FIGS. 22 and 23, pre-term cervical dilation can be
treated with a template 12 that is the impression "competent"
cervix. The cervical template 12 create vectors that contract the
circumference of the cervix. The incorporated energy delivery
device 18 contracts the native matrix and induces scar collagen.
The dilated cervical OS is tightened and the entire cervix is
strengthened. Energy delivery device 18 can be incorporated into
template 12 which can be the cervical conformer and inserted as a
vaginal obturator. It will be appreciated that template 12 can be
utilized for other functional treatments.
[0102] In another embodiment, template 12 is a functional appliance
that may be non conforming and can be separate or incorporated with
the energy delivery device 18. Orthodontic braces that are designed
with energy delivery device 18 are used to remodel the collagen of
the periodontal ligament and apply rotation and inclination vectors
on the tooth. In FIG. 24(a) orthodontic braces are coupled to RF
electrodes and associated power source. The orthodontic braces
function as a non-conforming force application surface that is
coupled to incorporated RF electrodes. FIGS. 24(b) and 24(c)
illustrates a orthodontic appliance that is a conforming template
12 coupled to RF electrodes. As a consequence, orthodontic
correction is more rapidly achieved than current modalities that
employ only mechanical forces. Orthodontic correction can also be
achieved with a conforming template 12 that is the corrected
impression of the patient's dentition.
[0103] For orthopedic applications, an external fixation device is
used as a non conforming functional appliance. This appliance is
used in tandem with an energy source device, including but not
limited to RF electrodes, that remodels the collagen of the callus
tissue. More accurate alignment of osteotomy and fracture sites are
possible with either a conforming or nonconforming brace that is
used in tandem or is directly incorporated into energy delivery
device 18. Improved range of motion of contracted joints and
correction of postural (spinal) deformities can be achieved with
this combined approach.
[0104] The ability to remodel soft tissue in anatomical structures
other than skin is dependent upon the presence of preexisting
native collagen. Induction of scar collagen is performed in tissue
devoid or deficient of native collagen.
[0105] Template 12 can be used to remodel the subcutaneous fat of
hips and thighs in addition to the tightening of the skin envelope.
The convolutions of the ear cartilage can be altered to correct a
congenital prominence. The nasal tip can be conformed to a more
esthetically pleasing contour without surgery.
[0106] Another application of the conforming energy delivery device
involves the noninvasive ablation of subcutaneous fat with
contraction of the overlying skin envelope. Altering the energy
delivery parameter (dose rate/dose) of the device provides a means
to concomitantly reduce contour with the ablation of fat while
contraction and conforming the overlying skin envelope to a more
aesthetic contour. Ablation of the subcutaneous fat is achieved
with a higher dose rate than collagen remodeling of the skin.
Various energy sources can be used including but not limited to
ultrasound, RF, incoherent and coherent light and thermal.
[0107] The combined ablation/remodeling application is facilitated
with surface hydration and the injection of an impedance altering
solution into the subcutaneous fat. The addition of Xylocaine and
Wydase into this (tumescent) solution provides anesthesia while
lowering the Ts (collagen shrinkage temperature) of the dermis and
fibrous septae.
[0108] Although various non-conforming ultrasonic devices can
noninvasively ablate fat, morphological outcomes are completely
different than outcomes achieved with conforming devices. Contour
reduction achieved with nonconforming devices may aggravate
pre-existing surface irregularities because skin contraction does
not occur. The apparatus 10 of the present invention, which may or
may not be coupled to a hydration device, reduces contour with fat
ablation while tightening the skin envelope in a noninvasive
manner.
[0109] Template 12 can be used with any modality that remodels
collagen. In addition to RF (molecular) remodeling of collagen,
cellular modalities that invoke the wound healing sequence can be
combined with a conforming esthetic template. Thermal and chemical
sources (glycolic acid) induce a low level inflammatory reaction of
the skin. Scar collagen induction and fibroblastic (cellular)
contraction are directed into converging and diverging vectors by a
conformer that produces a smoother and tighter skin envelope. In
addition to achieving a smoother and tighter integument, the
texture of the skin is also improved with this remodeling process.
Older or less compliant skin has a greater number of intermolecular
crosslinks in the dermal collagen than younger skin. Scar collagen
induction with cleavage of crosslinks will produce a softer and
more compliant skin envelope.
[0110] Referring now to FIGS. 25 and 26, template 12 can be
stationary or mobile. A hand held conforming template 12 that is
mobile provides the practitioner with greater flexibility to
remodel the collagen matrix. Pressure and impedance changes can
serve as a guide for the manual application of template 12. A hand
held template 12 with an incorporated energy source may be applied
over a conductive garment that provides additional three
dimensional conformance to the treatment area. The occlusive
geometry of template 12 enhances hydration and reduces impedance.
Less accessible areas can be remodeled with this particular device.
Template 12 of FIG. 25 may be made of a semi-solid material 35 that
conforms a lax skin envelope to an underlying soft tissue
structure. The semi-solid material customizes the creation of force
application surface 14 and reduces the need for precise fabrication
of an esthetic template. Suitable semi-solid materials include soft
plastics that are thermally and electrically conductive.
Additionally, the semi-solid material is semipermeable to provide
hydration. The permeability of the material can be altered
electrically or mechanically. For example, in one embodiment, the
application of an electrostatic charge through the material will
alter permeability. In another embodiment, externally applied
compression will increase permeability of the contact surface
material.
[0111] Controlled remodeling of collagen containing tissue requires
an electromagnetic device that lengthens or contracts the matrix
with a minimum of cell necrosis. Energy delivery device 18 can
include a plurality of RF electrodes with or without insulation.
The non-insulated sections of the RF electrodes collectively form
template energy delivery surface 20. In a similar manner, microwave
antennas, optical waveguides, ultrasound transducers and energy
delivery or energy remove fluids are used to form template energy
delivery surface 20. Individual electrodes and the like can be
multiplexed and to provide selectable delivery of energy.
[0112] Template 12 delivers both electromagnetic energy and
mechanical energy to the selected body structure. Suitable body
structures include but are not limited to, hips, buttocks, thighs,
calves, knees, angles, feet, perineum, the abdomen, chest, back
flanks, waistline, legs, arms, legs, arms, wrists, upper arms,
axilla, elbows, eyelids, face, neck, ears, nose, lips, checks,
forehead, hands, breasts and the like.
[0113] A variety of different mechanical forces can be applied to
tissue including but not limited to, (i) pressure, (ii) expansion,
(iii) stretching, (iv) extension, (v) prolongation, (vi)
lengthening or (vii) shearing. The pressure force can be a positive
pressure or a negative pressure. Positive pressure provides a
compression of collagen containing tissue, with converging and
diverging vectors, and negative pressure creates an extension of
collagen containing tissue with converging and diverging
vectors.
[0114] The duration and measurement of skin surface impedance
provides a delineation of a preferred treatment level within the
dermis. Surface impedance monitoring is used to determine the
amount of surface hydration that reduces ablation with the passage
of electromagnetic energy. However, impedance monitoring can also
be used to determine a preferred dermal level of treatment. More
superficial dermal treatment levels are used to treat wrinkles.
Deeper dermal levels are delineated for skin contraction and
three-dimensional conformance.
[0115] In various embodiments, energy delivery device 18 provides a
controlled delivery of electromagnetic energy to the skin surface
that does not exceed, 1,000 joules/cm2, or 10 joules/sec/cm2;
provides a controlled delivery of not exceeding 600 joules/cm2
during a single treatment session (during a twenty-four hour
period), operates in an impedance range at the skin surface,
provides a controlled delivery not exceeding 200 joules/cm2 during
a single treatment session, or not exceeding 10 joules/sec/cm2;
operates in an impedance range at the skin surface of, 70 ohms cm2
measured at a frequency of 88 Hz to 40 Kohms cm2 measured at a
frequency of 10 KHz; provides a controlled delivery of
electromagnetic energy to operate in a range of thermal
conductivity at a skin surface of 0.21 to 0.60 k; operates in a
range of compression force applied to the skin surface and/or the
underlying soft tissue anatomical structure not exceeding 400 mmHg,
not exceeding 300 mm, not exceeding 200 mmHg or not exceeding 100
mmHg.
[0116] To minimize and/or avoid surface ablation, saturation of the
stratum corneum, epidermis and conduit matrix is required. Surface
hydration with a measured impedance down to 70 ohms at a frequency
of 88 Hz is achieved. Target collagen containing tissues will
exhibit a higher than altered impedance that can be further
increased with the application of external compression.
[0117] FIG. 27 illustrates a schematic block diagram of an analog
embodiment of a specific impedance monitoring device 24 that can be
used with apparatus 10 and be incorporated into a feedback control
system. Impedance monitoring device 24 is used to control the
delivery of electromagnetic and mechanical energy to the skin
surface and underlying soft tissue structure to minimize, and even
eliminate, cell necrosis as well as blistering of the skin surface.
Impedance monitoring device 24 monitors other parameters including
but not limited to: if there is an open circuit, if there is a
short circuit, or if voltage and current is supplied to the tissue
for more than a predetermined maximum amount of time. Such
conditions may indicate a problem with apparatus 10 . When energy
delivery device 18 is one or more RF electrodes, a generator 26
supplies RF energy to the energy delivery surface 20. Generator 26
is turned on by a user operated switch 37 which provides a signal
to controller 35 to turn activate the generator 26. An output 30 of
controller 35 is coupled to an analog switch 32. When output 30
provides an "RF on" signal to the switch 32 an oscillator 34
coupled to an analog multiplier 36 through switch 32, supplies a
voltage of a known frequency to analog multiplier 36. An output of
analog multiplier 36 is coupled to a driver 38 which is coupled to
the input of an RF amplifier 40. The output of RF amplifier 40 is
coupled to circuit 42.
[0118] Current and voltage delivered to tissue is measured and an
RMS current ("I sub RMS") and an RMS voltage ("V sub RMS") are
determined. A voltage and current sensor 44 senses the current and
voltage delivered to tissue. Voltage and current sensor 44 includes
a low impedance current transformer 46 in series with generator 26
and a high impedance voltage transformer 48 connected in parallel
across generator 26. Current transformer 46 may have a 1:20 winding
ratio and a 50 ohm resistor in parallel with a secondary of low
impedance current transformer 46. Voltage transformer 48 may have a
20:1 winding ratio and a 1K ohm resistor in parallel with the
secondary of high impedance voltage transformer 48.
[0119] The output of low impedance current transformer 46 is
coupled to an RMS converter 50. RMS converter 50 converts a sensed
current to a DC signal to provide output 52, representative of I
sub RMS. The output of voltage transformer 48 is coupled to an RMS
converter 54. RMS converter 54 converts the voltage signal into an
DC signal to provide output 56, representative of V sub RMS.
[0120] The measured impedance, Z, is then calculated from the
measured I sub RMS and V sub RMS. Outputs 56 and 52 (V sub RMS and
I sub RMS) are supplied to an analog divider 58 which divides the V
sub RMS by the current I sub RMS to provide an output signal 60
representative of the measured impedance Z.
[0121] From the I sub RMS, V sub RMS and measured impedance Z,
impedance monitoring circuit 24 determines whether, (i) a short
circuit or open circuit condition exists, (ii) voltage and current
has been delivered for an amount of time exceeding a predetermined
maximum and (iii) whether controlled remodeling, contraction,
tightening, smoothing and the like is complete.
[0122] A short circuit condition is determined by comparing
measured impedance Z to a predetermined short circuit impedance
threshold at or below which short circuit is likely to exist ("Z
sub SC"). If the measured Z is at or below the Z sub SC, a short
circuit signal is provided to controller 35.
[0123] Impedance signal 60 is input to a short circuit detector 62
comprised of a comparator 70. A positive input 64 of the comparator
70 is connected to a potentiometer 66 which sets the threshold
impedance, Z sub SC. When impedance signal 60 causes the input at a
negative input 68 of a comparator 70 to be lower than that at
positive input 64, an "on" condition occurs at an output 72 of
comparator 70. This condition is communicated to controller 35
which provides a preprogrammed response that can include turning
off RF energy.
[0124] A current threshold detector 74 includes a potentiometer 76
coupled to a negative input 78. Potentiometer 76 sets the I sub
thresh level so that when a current is present, current detector 74
will indicate as such. The I sub RMS signal 52 is connected to a
positive input 80 of current threshold detector 74. Thus, when the
I sub RMS signal is greater than the value, I sub thresh, set by
the potentiometer 76, a positive voltage appears at an output 81 of
current threshold detector 74.
[0125] Similarly, a voltage threshold detector 82 includes a
potentiometer 84 connected to a negative input 86. Potentiometer 84
sets the voltage threshold at which threshold detector 82 registers
a positive output, V sub thresh, when a minimum voltage is present.
The V sub RMS signal 56 is input to a positive input 88 of the
threshold detector 82. If V sub RMS exceeds V sub thresh set by
potentiometer 84 a positive voltage appears at an output 90 of
voltage threshold detector 82.
[0126] Output 90 of the voltage threshold detector 82 is coupled to
an input 91 of AND gate 92 and the output 81 of current threshold
detector 74 is coupled to an inverted input 94 of AND gate 92. AND
gate 92 acts as an open circuit detector. When V sub RMS exceeds V
sub thresh and where the I sub RMS does not exceed I sub thresh, a
logic 1(not shown) will appear at an output 96 of AND gate 92
indicating an open circuit. Output 96 of AND gate 92 is coupled to
controller 35 to communicate the open circuit status.
[0127] The output 81 of current threshold detector 74 is also
coupled to an OR gate 98 which is coupled to a timer 100. If I sub
RMS exceeds I sub thresh, the output 81 of current threshold
detector 74 will present a logic 1 to the OR gate 98, causing the
OR gate output 102 to be high (logic 1) and turning on timer
100.
[0128] Similarly, output 90 of voltage threshold detector 82 is
coupled to OR gate 98. If V sub thresh is exceeded by V sub RMS,
the output 90 of voltage threshold detector 82 will present a logic
1 to the OR gate 98, causing the OR gate output 102 to be high
(logic 1) and turning on timer 100.
[0129] An output 104 of timer 100 is coupled to controller 35. When
timer 100 has been activated for an amount of time that exceeds a
preset threshold time, T sub max, output 104 will be a logic 1.
Timer 100 is reset with a user activated switch that is coupled to
the timer reset input 106, when apparatus 10 is reset.
[0130] A continuous comparison is made between Z and f(Z sub min).
It should be noted here that f(Z sub min) is continuously
calculated as f(Z) until a Z sub min is detected. The comparison is
continuously made between Z and f(Z) until Z sub min is
determined.
[0131] If measured Z is less than or equal to the Z sub target then
RF energy is continued to be supplied and steps described above are
carried out until a signal has been provided to controller 35 that
there is an open circuit signal, short circuit signal or a time
over signal. If the measured Z is greater than or is equal to "Z
sub target" then a signal is provided to controller 35. It is noted
that in this embodiment, Z has been inverted and shifted in order
to accommodate Z sub min determination.
[0132] A control device which controls an RF generator energy
output based on load impedance. The load impedance is used to
determine a preferred energy level, e.g., voltage, current or power
level, based on a specific system load curve for generator 26,
other power sources and/or application, as well as controlling the
delivery of the hydration medium from hydration medium source 11.
The control device then compares the actual energy level for
measured impedance with the desired energy level and adjusts the
generator output according to the difference between the two, i.e.,
preferably to minimize the difference between the two. A gradient
of tissue impedance is achieved that relates to the clinical
application. Superficial applications, including but not limited to
wrinkle treatment, will have a higher relative surface impedance
than deeper skin contraction applications which will have a lower
measured surface impedance.
[0133] The specific load curve preferably reflects the voltage,
current, power, for a range of impedance that will optimize
performance of apparatus 10 for a variety of different procedures
and anatomical body structures. The load curve may have various
forms, for example, it may be continuous or may be stepped. The
load curve may vary from power source to power source, or for
different body structures and/or applications. In a one embodiment
using apparatus 10, different impedance ranges may be identified at
which different energy requirements exist. Initially tissue
impedance is in a lower range. In the lower ranges more current is
required to provide enough power. A second, mid-range of impedances
requires enough power to maintain the process. A third range of
higher impedances may be required at the end of the process.
[0134] In one embodiment, impedance is monitored to measure the
amount of skin surface hydration that is required for the
transcutaneous delivery of RF energy as well as other
electromagnetic energy delivered to the collagen containing
tissue.
[0135] Referring now to FIGS. 28 through 31 a flow chart
illustrates a method for carrying out a microprocessor controlled
embodiment of the present invention. When the system is turned on
(block 200), the variables including Z sub min, V sub thresh, I sub
thresh, time over, and Z sub initial, are initialized (block 201).
The system continues to look for the activation of the RF switch
(block 202). When the RF switch is turned on, the interrupts are
set for RF Switch (block 203), for Short Circuit (block 204), and
Open Circuit (block 205) so that when one of these interrupt
conditions occur, the microprocessor automatically goes to the
instructions associated with block 234.
[0136] After the interrupts are set, the timer is started (block
206). A sequence is run to check the RF amplifier health (block
207), e.g., to look for an Amplifier On signal or to check if
certain voltages are in a suitable range. If the amplifier is
operating properly, RF energy is turned on (blocks 208 and
209).
[0137] If the amplifier is not operating correctly, an RF Off
request is made (blocks 209 and 210) and a Hardware Failure Alert
flag is set (block 211). The system looks for a hardware failure
flag (block 233). When the hardware failure is detected, the
controller provides a hardware failure alert indication and shuts
off. (blocks 243 and 244).
[0138] If hardware failure is not indicated (block 233), then V sub
rms and I sub rms is read (block 235) to determine if any voltage
or current is being supplied by the system (block 236). When the
system is first initialized, until the instruction to turn on
energy in block 209 is reached, there should be no current or
voltage. If there is a voltage or current with the RF request off,
then there is a hardware failure. A hardware failure alert is
indicated and the program is stopped (blocks 243 and 244).
[0139] If RF energy is turned on (block 209), then the V sub rms
and I sub rms are read and the impedance, Z, is calculated by
dividing the V sub rms by the I sub rms. (block 212). The
controller checks to see if the V sub enable and 1 sub enable flags
are set. (block 213). These flags are set when a minimum threshold
voltage is present and a minimum threshold current is delivered
through the electrodes of the device. (blocks 214, 215, 216, and
217).
[0140] If the V sub enable and 1 sub enable flags are set (213) the
software looks for a time over condition to determine if the device
has been on for a period of time in excess of a maximum. If a time
over condition is recognized, the timer flag is set, RF energy is
turned off (blocks 218 and 219) and a hardware failure check is run
(block 233).
[0141] After looking for a time over condition, the controller
checks for a short circuit or open circuit condition. If a short or
open circuit exists, the corresponding short circuit or open
circuit bit is set (block 220), RF energy is turned off (block
221), and a hardware failure check is run (block 233).
[0142] The controller checks again for V sub enable and I sub
enable in block 222, before proceeding to the threshold determining
portion of the circuit illustrated in FIG. 27. If the voltage or
current did not exceed V sub thresh or I sub thresh in blocks 214
and 216, the controller iterates the sequence beginning at block
212 for detecting time over, short circuit, open circuit, i.e., the
coagulation complete detection enable. This enables the device to
wait until enough current and voltage is delivered to the circuit
to check for the coagulation complete condition.
[0143] If the V sub enable and 1 sub enable flags are set, the
short circuit and open circuit bits are not set (block 220), and
the time over condition does not yet exist (block 219), the
measured impedance used to determine completion of matrix
remodeling is as follows. Remodeling of the matrix into a more
compact configuration will alter the ECF/hydration which will be
measured as an increase of impedance. Desiccation of the matrix is
avoided by ceasing the delivery of electromagnetic radiation when
the impedance is above the allowed range.
[0144] The Z initial flag is set during the first iteration and Z
sub min is initially assigned the measured impedance value (blocks
223-225). Initially, Z sub min is the same as the measured
impedance and thus block 227 is bypassed at block 226. A
calculation is made of f(Z sub min) (block 228). As long as the
measured impedance is less than the f(Z sub min), the sequence is
iterated (229, 231). In the next iteration of blocks 223-231, the
newly measured impedance is compared to the previous measured
impedance which has been assigned Z sub min (block 226). As long as
the impedance is decreasing, Z sub min will be reassigned the new
value of the measured impedance (blocks 226 and 227) and the steps
repeated. When the measured impedance is greater than or equal to
f(Z sub min), i.e. the threshold impedance, the coagulation
complete flag is set (block 230). If coagulation complete flag is
set, the RF is turned off (block 232) and the hardware failure
check is run.
[0145] If after the initial run through the program a hardware
failure alert occurs (block 233, 236) or an interrupt occurs, the
program determines the cause and indicates as such (blocks
233-242). The V sub rms and I sub rms are read, (block 235). If no
current or voltage is being delivered to the system, the controller
checks to see if the open circuit, short circuit or time over flags
have been set (block 237). If so then a signal indicates which
flags have been set, and the program is returned to start (blocks
240, 242). Similarly, the controller checks for the coagulation
complete flag (block 239). If there was the coagulation complete
flag has been set, it will be indicated for ten seconds (block
241). If not, it will be indicated as not complete (block 240) and
the program will return to point at the start (block 242).
Preferably the electrical components selected to carry out the
steps of FIGS. 28 through 31 are adapted to provide a complete
iteration of all the steps at least every 1/50 second.
[0146] The foregoing description of a preferred embodiment of the
invention has been presented for purposes of illustration and
description. It is not intended to be exhaustive or to limit the
invention to the precise forms disclosed. Obviously, many
modifications and variations will be apparent to practitioners
skilled in this art. It is intended that the scope of the invention
be defined by the following claims and their equivalents.
* * * * *