JP2000300683A - Dental and medical cordless laser and method for sterilizing organ tissue by hardening compound material with using the same - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide low-cost miniaturized independent type efficient and chargeable dental or surgical laser equipment by making a battery and a semiconductor pumping laser adjustable to the light absorbing characteristics of a target by selecting the output power of an output laser beam to a prescribed value even when the power consumption of the laser equipment is maximum during laser operation. SOLUTION: The heat exchanger of a thermoelectric heating and cooling type performs the tuning control of a microchip laser and temperature control. The temperature and diffraction factor of crystal are adjusted by heating and cooling and the output wavelength of a laser beam radiated from the microchip laser is adjusted. An external reflecting means 13 is arbitrarily selectively attached to a housing 1 so that the laser beam can be reset to the target portion of a patient having a difficulty to move and arrive in the optical path of the output laser beam. A battery 2 is selected so as to provide the capacity of the output laser power of 10 W at a maximum and 20 mW at a minimum for power consumption during laser operation.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

FIELD OF THE INVENTION The present invention relates to the use of medical laser equipment to cure dental and surgical composites and to sterilize biological tissue, producing a single line laser beam from a diode-pumped solid-state microchip. About the method.

[0002]

2. Description of the Related Art Known dental and surgical lasers are large and are connected to hand-held equipment by power, coolant, and fiber optic cables. These devices are
Wall plug efficiency
A gas-filled plasma tube with a ciency of less than 0.01% is inefficient and consumes more than 2000 watts of power. US Pat. No. 5,334,016 G
Oldsmith et al. disclose an argon laser that cures dental materials in combination with a helium-neon laser. This system requires a separate housing with forced air cooling and a fiber optic cable to transmit the laser beam to a separate handheld device. This laser wavelength does not match the peak absorption wavelength of the composition of the material to be cured. Ba in U.S. Pat. No. 5,388,987
doz et al., US Pat. No. 5,548,604, Tope.
1 also discloses a dental laser device. However, they are all large fixed devices connected to separate hand-held devices by optical fibers and power cables. These are not cordless devices. The wavelength of these lasers does not match the peak absorption wavelength of the material to be cured, and a great deal of energy is wasted.

[0003] Cipolla is disclosed in US Pat. No. 5,616,614.
No. 1 discloses an argon laser dental instrument and a method for curing dental composites. However, the laser beam contains a large number of wavelengths, some of which are not useful for curing and must be filtered. Thus, this system represents an inefficient way to generate the laser beam required for curing. In addition, the laser system is an argon gas laser, which requires a high power cooling system to operate. In addition, argon gas lasers require high voltage and high current power supplies. Therefore, this device cannot be made into a small, hand-held, stand-alone device. It is necessary to connect large fixing devices to hand-held parts separated by optical fibers and cables. In addition, the output of an argon laser consists of a number of wavelengths from blue to green, of which only the 488 nm blue line is useful for curing. Because this beam is collimated, it has a constant power along the length of the radiation of the beam. As a result, the surface layer begins to cure before the deeper layer, the cure is uncontrolled and bubbles are formed inside.

No. 4,940,411 to Vasseliadis et al. Discloses a 1.06 μm pulse Nd: Y.
Disclosed is a method of using an AG laser to annihilate and sterilize dental pulp tissue. This device is neither stand alone nor cordless, and the wavelengths generated cannot be used to cure the composite. In addition, sterilization is performed by excision and cauterization, and cannot be performed without killing living tissue. Also, U.S. Pat. No. 5,507,739 discloses dual wavelength lasers for dental treatments, which are not useful for curing composites or for sterilizing tissue.
Is the infrared wavelength.

[0005] Paghdiwala is disclosed in US Pat.
No. 01,171 discloses an ablation focused pulse Er: YAG laser that can be used in dentistry. Although the laser beam is generated in a hand-held instrument, its power supply and water-cooled pump are external, not stand-alone of the hand-held instrument, and does not disclose how to cure the composite or sterilize tissue.

[0006] Kowallyk et al. In US Patent No. 5,45.
6,603, red attenuated by some pigment material,
A method for removing tooth erosion using a pulsed frequency dual laser emitting green, deep blue, and ultraviolet (UV) light is disclosed. However, this patent does not mention a wavelength that matches the maximum absorption wavelength of the medical complex for curing. Moreover, the device is not small and not a hand-held or stand-alone device.

[0007]

There remains a need to develop small, stand-alone, efficient, rechargeable, dental or surgical laser devices that can be manufactured at low cost. There also remains a need to provide an efficient method of laser curing dental and surgical composites and laser sterilizing tissue. An object of the present invention is to satisfy the above-mentioned needs.

[0008]

SUMMARY OF THE INVENTION The present invention is a small, rechargeable, hand-held laser device for surgical and dental procedures, comprising a single hand-held housing containing a semiconductor pumping laser. The housing has a microtip laser in optical contact with and pumped by the pumping laser, and an internal reflector mounted within the housing to send the laser beam from the microchip laser to the target. Means, an output lens mounted at one end of the housing remote from the internal reflection means for conditioning the output laser beam, and at least one electrically connected to the charging electrode to serve as a sole power source. Rechargeable battery, control means mounted on the housing, responsive to fingertip pressure and electrically connected to the battery and the pumping laser, and a charging electrode for charging the battery when the housing is plugged into the charger. And are stored. The battery and pumping laser are selected such that the power consumption of the laser equipment during laser operation is at most 10 watts and the output power of the output laser beam is at least 20 milliwatts and the output power is targeted. Can be adjusted with respect to the light absorption characteristics.

Also, the method of the present invention is a method of curing a photopolymerizable composite material useful for surgery, dentistry, and medical treatment using a diode-pumped solid-state laser generator, and sterilizing living tissue. Specifically, the site is sufficiently exposed so that the laser beam can illuminate the living tissue site to be sterilized, the first selected solid-state laser microchip is pumped with a diode laser, and Passing a generated laser beam through a lens to generate a divergent beam of a single selected wavelength ultraviolet wavelength laser beam in a hand-held, stand-alone, diode-pumped solid state laser generator; The wavelength of the light emitted from the selected microchip is set to 360n at the maximum.
The biological tissue site where the divergent beam should be sterilized for a time sufficient to kill living microorganisms contaminating the tissue, selected as m to be the maximum absorption wavelength of the contaminated biological tissue. A sufficient amount of the selected photopolymerizable medical composite is placed at the repair site to effect the repair, and the device is switched to a curing mode of operation by switching means, thereby at least a second selection within the device. The pumping of the selected solid-state laser microchip to a single band blue wavelength laser of the selected wavelength in the instrument, with the selected wavelength emitted by the second selected microchip being at most 480 nm. Generate and focus the beam beam, pass the light beam through a focusing lens, and select the wavelength to be the maximum absorption wavelength of the selected composite A time sufficient to achieve curing of the material, is characterized in directing a laser beam of a single band wavelength focused from the device to the material.

[0010]

BRIEF DESCRIPTION OF THE DRAWINGS The above and other objects and advantages of the present invention will become more apparent from the following drawings and description of preferred embodiments.

The present invention is a lightweight, ergonomic, hand-held device for use in dentistry, oral and orthopedic surgery for medical procedures such as sterilization of target sites (sometimes simply sites) and photopolymerization and curing. It is a cordless, portable, stand-alone laser device. The output wavelength from the microchip laser 6 shown in FIG. 1 matches the peak absorption wavelength of the target material, and the output power from the microchip laser 6 matches the specific requirements of the target material. Examples of medical, surgical, and dental target sites include skin surfaces, gingiva, tooth surfaces, bone surfaces, bone interiors, and internal tissue from surgical incisions. Other examples of surgical and dental sites are materials that can be cured by photopolymerization.

The entire device of this embodiment is housed in a single, hand-held, ergonomic housing 1 shown in FIG. This device is powered by at least one rechargeable battery 2. This battery 2 corresponds to FIG.
As shown in FIG. 3, the device is electrically connected to the charging electrode 3 by a wire so that the device can be charged when the device is inserted into the charger 4. Semiconductor pumping laser 5 electrically connected to variable power diode 11 (FIG. 1) by wires
Is at least one in optical contact with the pumping laser 5, as shown in FIGS. 2A, 2B and 2C.
The laser radiation from the microchip lasers 6 is induced. "Optical contact" means that the laser beam from one component is oriented in the line-of-sight direction so as to irradiate and stimulate an adjacent component. Details of portion L of FIG. 1 are shown in FIGS. 2A, 2B, and 2C, which are enlarged views of three embodiments of the microchip laser 6 assembly. All of the components shown in FIG.
Attached inside the housing 1 and connected and aligned with each other. An internal reflection means 7 is mounted on the optical path of the laser beam inside the housing 1. The laser beam from the microchip laser 6 is reflected by the reflecting means 7 and sent to the target site as shown by the arrow in FIG. The internal reflection means 7 is selected from any one of a mirror, a prism, and an optical fiber.
Each microchip laser 6 is composed of at least two crystals. The crystals are brought into optical contact and joined to form a heterojunction. An output filter 8 is mounted inside the housing 1 between the microchip laser 6 and the internal reflection means 7. Internal reflection means 7
An output collimating lens 9 is attached to the distal end of the housing 1 at one end away from the housing. As shown in FIG. 1, a finger control button 10 is provided which is a control means for turning on / off the current flowing through the wire to the pumping laser 5 and thereby turning on / off the laser.
The variable power diode 11 is electrically connected by wires to the control button 10, the pumping laser 5, and the battery 2, and can change the power from the battery 2. By varying the power, the power of the output laser can be tailored to the specific light absorption characteristics of the selected target material. Microchip laser 6
Control and temperature control of the thermoelectric heating and cooling type heat exchanger 1
2 is performed. The output wavelength of the laser beam emitted from the microchip laser 6 is adjusted by adjusting the temperature and the refractive index of the crystal in the microchip laser 6 by heating and cooling. The housing 1 is optionally equipped with external reflecting means 13 which can be moved in the path of the output laser beam to redirect the laser beam to a target site of the patient which is difficult to reach. The external reflection means 13 is selected from one of a mirror, a prism, and an optical fiber. Battery 2 is selected so that the power consumption during laser operation is at most 10 watts and a capacity of at least 20 milliwatts of output laser power is obtained. All of the above features are features of each of the following three embodiments of the microchip laser 6 assembly.

A first embodiment of the microchip laser 6 is shown in FIG. 2A, preferably with a heterojunction crystal, N
d: with a single microchip laser 6 consists of YAG / KNbO _3. The laser emits a wavelength of at most 480 nm, preferably at least 472 nm, and at most 474 nm, useful for curing dental and surgical materials that can be cured by photopolymerization. In another example of this embodiment, a microchip
Laser 6 provides 210 to 360 nm, preferably 354 nm, useful for sterilization of surgical and dental target sites.
Emit a wavelength of ~ 356 nm. This microchip
Laser 6 is preferably a heterojunction crystal, Nd: YAG
/ KNbO ₃ / LBO, and the laser for sterilization may be comprised of Nd: YVO ₄ , KTP, and LBO crystals, denoted as Nd: YVO ₄ / KTP / LBO. Because microorganisms are more sensitive to ultraviolet (UV) light than visible light, the output power of the sterilization laser of the embodiment is significantly lower than the output power during sterilization with visible light. In another example of this embodiment, the active Q-switch electrode 14 is preferably a KNbO
₃ and attached to the control button 10 to perform active Q switching.

In a second embodiment, shown in FIG. 2B, two different microchip lasers 6 are in optical contact with the pumping laser 5 in the same housing 1 as shown in FIG. The microchip laser 6 includes Nd: YAG / KNbO ₃ , which is a laser output having a wavelength of 472 nm to 474 nm for curing, and 354 for sterilization.
Nd: YA which is a laser output with a wavelength of
G / KNbO ₃ / LBO is preferred. In another example of this embodiment, the active Q-switch electrode 14 is the KNb of the microchip laser 6, as shown in FIGS. 1 and 2B.
Attached to O ₃ and control button 10 for active Q switching. A switch for switching between the UV laser beam and the blue laser beam is a control button 10.
Therefore, the same equipment is used for sterilization and curing by photopolymerization. As in the embodiment of FIG.
The changeover switch 16 may be separately prepared.

In the third embodiment shown in FIG.
Absorption crystal 15, preferably Cr: YAG, has laser output
Can be passively Q-switched
Also the laser cavity of one microchip laser 6
It is placed in the space. This allows for high peak power and
And high efficiency pulsed laser beam output
You. The advantages are more complete penetration and curing, and
Better heat loss and better control of thermal motion.
In one example of this embodiment, the preferred microchip
At least one of the lasers 6 is Nd: YAG / Cr: Y
AG / KNbO _ThreeWhich is a minimum of 472 nm,
Emit an output laser beam wavelength of up to 474nm
You. In another example of this embodiment, the preferred micro
At least one of the chip lasers 6 is Nd: YAG / C
r: YAG / KNbO_Three/ LBO, which is the output level
User wavelength is at least 354 nm and at most 35
Effective for dental and surgical target sites that are 6 nm
Emit UV light for efficient sterilization. In other examples
Means that two or more pulsed microchip lasers 6
Housed in the same housing 1 and switch between different lasers.
Switch for performing switching is built into control button 10.
It is rare. Therefore, sterilization steps in medical procedures
No time is wasted between the curing steps.

FIG. 3 shows another embodiment in which two microchip lasers 6 are arranged in parallel and two internal reflection means 7 for each laser beam are arranged in the housing 1. is there. In this embodiment, a focusing lens is used as the output lens 17. Further, a finger control switch 10 for turning on / off the laser is disposed on the laser beam emission side of the grip portion of the housing 1, and a changeover switch 16 for switching the light operation mode from the sterilization operation to the curing mode for curing the target material is provided on the rear side of the housing. Has been placed.

A method for curing a surgical and dental composite and sterilizing a living tissue using the above embodiment will be described below. First, the site is exposed so that the laser beam can irradiate the site. The solid microchip 6 is then pumped by the diode laser 5, thereby producing a divergent diverging beam of a single band ultraviolet laser beam. As described above, the ultraviolet microchip 6 is made of Nd: YVO ₄ / KTP / LBO or N
d: YAG / KNbO ₃ / BBO.
The microtip 6 crystal laser material can be optionally contacted, bonded by thermal diffusion, or bonded by optical epoxy. The solid microchip 6 of the present embodiment is a solid laser crystal material assembled so that the volume is less than 1 cubic centimeter. The microchip 6 can be composed of a plurality of such crystalline materials, all contained within the optical cavity. The output wavelength of the UV laser is selected between 210 nm and 360 nm to optimize the differential absorption of the killed bacterial cells.
and the minimal absorption of healthy living tissue, so that the living tissue at the site to be repaired is not killed. The diverging beam of the ultraviolet laser beam is directed at a biological tissue site for a time sufficient to kill all bacterial life forms that contaminate the site. The beam diverges over the area to be sterilized.

Next, in the curing mode of operation, a sufficient amount of the selected photopolymerizable medical composite is placed at the site to be repaired and restored. The device 1 is then switched to the curing operating mode by the switching means 16 just above the on / off switch 10. This initiates pumping of at least the second selected solid-state laser microchip 6, producing a selected wavelength of at most 480 nm.
The wavelength is chosen to be the maximum absorption wavelength of the material to be cured. After being reflected by the rotating mirror 7, the beam is focused through the lens 17. The microchip 6 selected in this embodiment includes Nd: YAG / KNbO ₃ and N
d: selected from the group consisting of YVO ₄ / KNbO ₃ . The focused beam is allowed enough time for curing to begin,
Aim at the selected composite light-activated material. Power consumption during laser operation is at most 10 watts and the maximum laser output power is at least 20 milliwatts. The output power is controlled by the diode laser drive electronics 4
Adjusted to the requirements of the target material.

In order to increase the completeness of the cure,
The beam is focused on the tissue-composite interface and then moved through the composite toward the surface away from the interface. This eliminates the formation of air bubbles and enhances the bond between the composite and the living tissue to be repaired.

If only a specific wavelength of the laser beam is generated by the microchip 6, no filter is needed and its power can be used more efficiently than in the prior art. Configuration of device 1 including rechargeable battery 2 with charging electrode 3, diode laser drive electronics 4, pumping diode laser 5, microchip 6, mirror 7, and lens 17 because it requires little power All of the elements are housed in a unit that is a hand-held, ergonomic, cordless, stand-alone, portable, lightweight equipment housing not possible with the prior art. The microchip 6 is made of any suitable laser material that is not limited to a solid material.

The Q-switch pulse laser beam is:
Used to further increase the efficiency and control of the curing process. A focused beam is better than a collimated beam for curing because a deep layer of photopolymerizable medical composite can be photoactivated before the surface layer is cured.

The device 1 can be used only in the curing mode, and can also be used only in the sterilization mode. Alternatively, it is first used for sterilization of the tissue site, and then the restorable surgical or dental light activated composite is cured. With the switch 9, only one mode is performed at a time. This combined use saves a great deal of time in surgical and dental procedures while reducing the potential for infection much more than in the prior art.

Thus, for all of these reasons, the method of the present invention proves to be a significant advance in the art of hardening and sterilizing composites in surgery and dentistry and has considerable commercial advantages.

Although specific process steps, structures, and methods have been shown and described herein, it should be understood that changes can be made without departing from the spirit and scope of the basic inventive concept. It will be clear to the trader. The invention is not limited to the specific process steps, structures, and methods described herein, except as by the appended claims.

[0025]

As described in detail above, it is possible to obtain a cordless, portable, independent power supply for medical and dental laser equipment capable of generating a wavelength optimal for use. In addition, the present invention can practically and efficiently sterilize living tissue with a laser beam without killing the living tissue. Further, the present invention can similarly cure medical composites with a laser beam, overcoming problems such as incomplete curing of the prior art. Further, the present invention can save time and reduce the incidence of infection without killing living tissue, and in a single operation with a single instrument, can sterilize tissue and cure medical composites. it can.

[Brief description of the drawings]

FIG. 1 illustrates a hand-held, stand-alone, rechargeable laser dental and surgical instrument of one embodiment of the present invention.

FIG. 2 is an enlarged view of a portion L shown in FIG. 1 showing different examples of the microchip laser of the embodiment of FIG. 1;

FIG. 3 is a cross-sectional view of a second embodiment of a laser dental and surgical instrument.

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 Device 2 Battery 3 Charging electrode 4 Diode / laser drive electronic component 5 Diode / laser 6 Microchip 7 Rotating mirror 8 Lens 9 Switching means 10 ON / OFF switch

 ────────────────────────────────────────────────── ─── Continued on the front page (72) Inventor Yutaka Shimoji United States 34624 Florida Florida Clearwater University Coat 2125 F-term (reference) 4C026 AA01 BB08 FF22 FF33 FF34 GG01 GG06 HH02 HH04 HH06 HH13 HH17 HH21 HH22 4C052 AA06 AA17 BB11 HH01 MM10 4C058 AA12 AA13 AA28 BB06 KK02 KK26 KK27 KK28 KK32 KK46 4C082 RA07 RC09 RE22 RE34 RE35 RJ01 RJ06 RL02 RL04 RL06 RL13 RL17 RL21 RL22

Claims (10)

[Claims] 1. A small, rechargeable, hand-held laser device for surgical and dental procedures, comprising a single hand-held housing containing a semiconductor pumping laser, and optically contacting and pumping the pumping laser. A microchip laser pumped by the laser, internal reflecting means mounted in the housing to send the laser beam from the microchip laser to the target, and internal reflecting means to condition the output laser beam. An output lens mounted on one end of the remote housing, at least one rechargeable battery electrically connected to the charging electrode to serve as a single power source, and a pressure on a fingertip mounted on the housing. Control means responsive and electrically connected to the battery and the pumping laser; A charging electrode for charging the battery when the housing is plugged into the charger, wherein the battery and the pumping laser are such that the power consumption of the laser equipment during laser operation is at most 10 watts and the output laser A laser device wherein the output power of the beam is selected to be at least 20 milliwatts and the output power is adjustable with respect to the light absorption characteristics of the target. 2. A thermoelectric heat exchanger that is in thermal contact with the microchip laser and controls the temperature of the microchip laser to adjust the output wavelength of the output laser beam generated by the microchip laser. And attached to the housing and electrically connected to the battery, control means, pumping laser to increase or decrease the output power of the output laser beam,
2. The laser device according to claim 1, further comprising a variable power diode for adjusting an output power according to a light absorption characteristic of the target. 3. A small, rechargeable, handheld, multiple microchip laser device for surgical and dental procedures, wherein at least one is in optical contact with at least two microchip lasers. A single hand-held housing containing the semiconductor pumping laser of the present invention, switching means electrically connected to the microchip laser for switching from one microchip to another, and an electrical connection to the switching means and the laser. At least one rechargeable battery electrically connected to serve as a sole power source during laser operation; and a charge electrically connected to the battery for charging the battery when the housing is plugged into the charger. Electrodes and laser
At least one internally reflecting means mounted within the housing to direct the beam from the microchip laser to the target, wherein the battery consumes at most 10 watts of equipment during laser operation and the output laser A laser device wherein the output power of the beam is selected to be at least 20 milliwatts and the output power is adjustable with respect to the light absorption properties of the target. 4. At least one of the at least two microchip lasers is in thermal contact with a thermoelectric heat exchanger to enable continuous tuning of the output laser wavelength and to control the output laser beam. 4. The multiple microchip laser device of claim 3 including a variable power diode mounted on the inner surface of the housing for controlling output power and electrically connected to the battery, switching means, and the pump laser. . 5. A small, rechargeable, hand-held, passive Q-switched pulsed laser device for surgical and dental procedures, comprising a small hand-held housing containing at least one microchip laser. A saturable absorbing crystal disposed in at least one laser cavity of the at least one microchip laser for passively Q-switching the output laser beam; A semiconductor pumping laser in contact therewith, at least one rechargeable battery electrically connected to the control means and the pumping laser to act as a sole power source during laser operation; and electrically connected to the battery. A charging electrode that charges the battery when the housing is inserted into the charger, and a laser
At least one internally reflecting means mounted inside the housing for directing a beam from the microchip laser to the target, wherein one of the microchip lasers is hardened by photopolymerization. A blue laser with an output beam wavelength that matches the peak absorption wavelength of the material, the battery is sized such that the device is stand-alone and handheld, and the device consumes up to 10 watts during laser operation; And a laser device wherein the output power of the blue laser is selected to be at least 20 milliwatts and the output power can be adjusted for the light absorption characteristics of the selected target material. 6. A method of using a diode-pumped solid-state laser generator to cure a photopolymerizable composite useful in surgery, dentistry, and medicine and to sterilize biological tissue, wherein the laser beam is sterilized. Exposing the living tissue site sufficiently to irradiate the site; pumping the first selected solid state laser microchip with a diode laser and passing the laser beam generated from the microchip through the lens Generating a divergent beam of an ultraviolet wavelength laser beam of a single selected wavelength in a hand-held, stand-alone, diode-pumped solid-state laser generator; and radiating from the first selected microchip. The wavelength of the light to be emitted is up to 360 nm
The divergent beam is selected to be at the wavelength of maximum absorption of the contaminated living tissue and the divergent beam is applied to the living tissue site to be sterilized for a period of time sufficient to kill living microorganisms contaminating the tissue. Orienting; placing a selected amount of the photopolymerizable medical composite at the repair site in an amount sufficient to achieve the repair; and switching the device to a curing mode of operation by switching means, thereby at least a first time within the device. Initiating the pumping of two selected solid-state laser microchips and a single of the selected wavelengths within the instrument, with the selected wavelength emitted by the second selected microchip being at most 480 nm. Generating and focusing a band blue wavelength laser beam, passing the light beam through a focusing lens; Methods including selected such that the maximum absorption wavelength of the composite for a time sufficient to achieve curing of the material, and the step of directing a laser beam of a single band wavelength focused from the device to the material. 7. A step of placing a selected photopolymerizable medical composite in the repair site in an amount sufficient to effectuate the repair, and attaching the at least one selected solid microchip to the at least one diode. Pump with laser,
Generating a single-band blue-wavelength laser beam of a selected wavelength inside a hand-held, stand-alone, diode-pumped solid-state laser generator by passing the laser beam generated by the microchip through a focusing lens; Focusing the laser beam at a wavelength of at most 480 nm and selecting the wavelength to be the maximum absorption wavelength of the selected material, leaving the device for a sufficient time to achieve curing of the material. Directing a focused blue wavelength laser beam at the material. 8. The step of directing the laser beam at the material comprises first focusing the focused laser beam at a boundary between the biological tissue and the material, and then moving the focus away from the boundary and toward the surface of the material. 8. A method according to claim 6 or 7, wherein the method is effected by terminating at a surface remote from the surface, so that the material cures first at the boundary and finally at the surface. 9. A method of sterilizing living tissue, the method comprising the steps of: exposing a living tissue portion to be sterilized sufficiently by a laser beam; and at least one selected solid-state laser. By pumping the microchip with at least one diode laser and passing the laser beam generated from the microchip through a lens, a single selection is made inside a hand-held, stand-alone, diode-pumped solid-state laser generator. Generating a divergent ultraviolet wavelength laser beam in the selected wavelength band, and setting the wavelength of the light to at most 360 nm for a time sufficient to kill living microorganisms contaminating tissue. It contacts the tissue site beyond the focal point of the beam, and consequently the laser beam covers the area to be sterilized. Directing the beam as a diverging beam having a sufficient cross-sectional area onto a living tissue site to be sterilized. 10. A method of curing a medical composite having a light-activated curing mechanism, the method comprising directing a focused Q-switched pulsed laser beam at the composite to effect curing of the composite. A method wherein the laser beam is generated from at least one laser material at a single band blue wavelength, the wavelength being at most 480 nm, being selected to be the maximum absorption wavelength of the composite.