CN220089460U

CN220089460U - Detection device for self-fluorescence tissue

Info

Publication number: CN220089460U
Application number: CN202321101489.2U
Authority: CN
Inventors: 陈亮; 李健聪; 王鹏博; 王越桥; 范利娟
Original assignee: Jiangsu Baining Yingchuang Medical Technology Co ltd
Current assignee: Jiangsu Baining Yingchuang Medical Technology Co ltd
Priority date: 2022-05-09
Filing date: 2023-05-09
Publication date: 2023-11-28
Anticipated expiration: 2033-05-09
Also published as: CN116559988A

Abstract

An apparatus for detecting self-fluorescent tissue, the optical system of which comprises the following optical elements: a laser light source (1) for emitting modulated laser light; a light source side lens (2) for collimating laser light emitted from the laser light source (1); a fiber side lens (3) for collimating fluorescence returned after excitation of the laser; an optical fiber (4) for transmitting laser light to the distal end on the laser excitation light path and transmitting fluorescence light to the proximal end on the fluorescence receiving light path; a photosensor (6) for sensing the returned fluorescent signal; the optical system further comprises a fluorescence filter (9) for filtering out stray light. The detection device of the self-fluorescence tissue can excite enough self-fluorescence energy under the condition of high laser density, and accurately, quickly and noninvasively and efficiently identify parathyroid glands in operation.

Description

Detection device for self-fluorescence tissue

Technical Field

The present utility model relates to an apparatus for detecting an autofluorescence tissue, and more particularly, to an apparatus for detecting an autofluorescence tissue using an autofluorescence principle.

Background

The self-fluorescent tissue is a tissue which can excite a fluorescent signal with another wavelength under the excitation of laser with a certain wavelength, such as parathyroid gland tissue, and can generate weak fluorescence with a peak value of 820-830 nm under the excitation of laser with a wavelength of 785 nm.

The human body has two pairs of parathyroid glands, which are respectively positioned at the middle and lower parts of the back surfaces (or buried in) of the left and right thyroid glands. Parathyroid gland is brown yellow, is similar to soybean, and has the main functions of secreting parathyroid hormone (PTH for short) and regulating calcium and phosphorus metabolism in a body. If the parathyroid gland of the human body is hypofunctional or the parathyroid gland is thoroughly removed due to reasons (such as careless false extraction when thyroid surgery is cut off), PTH secretion is insufficient, blood calcium is gradually reduced, blood phosphorus is gradually increased, low blood calcium tic is caused, and death is even possible in severe cases.

Parathyroid glands weigh 35-45mg, are about 2x3x4mm in size, are very small in size, and the location of the parathyroid glands is not constant: the upper parathyroid gland is relatively constant, with about 77% located near the cricothyroid joint, 22% located very posteriorly from the thyroid gland, and only about 1% located posterior to the pharynx, posterior to the esophagus; the difference of the position of the lower parathyroid gland is large, 42% is positioned at the front and back of the hypothyroid pole, 39% is positioned at the thymus tongue (namely, the lower parathyroid gland is searched by using the pectoral ligament), 2% is positioned in the upper mediastinum thymus, 15% is positioned at the tracheal duct near the thyroid body, and 2% has variation. Therefore, in thyroidectomy for removing thyroid tumor, it is difficult to distinguish parathyroid gland from peripheral tissues such as thyroid gland, fat and the like with naked eyes, and great hidden trouble is brought.

According to the related research at home and abroad, certain tissues with fluorescent characteristics of a human body can be wrapped by a muscle film, and the tissue needs to be excited by laser with relatively high intensity, basically from tens of milliwatts to hundreds of milliwatts, and the intensity of the excited fluorescent light is very weak. If the parathyroid gland is excited by 785nm excitation light, the autofluorescence phenomenon with peak value between 820 and 830nm wavelength can be generated, but the excitation efficiency of the autofluorescence is extremely low, and under 20mW laser excitation, only extremely weak fluorescence with about 100pW can be generated, and the light intensity difference is 2x 10 ⁸ The 785nm laser signal is extremely difficult to filter. Although the fluorescence filter can effectively remove signals beyond a stop band, such as 785nm laser signals, the OD (optical density) value cannot be infinitely increased in engineering, which is the best possible OD6 for domestic and civil use at present, because OD is an abbreviation of optical density and represents the optical density absorbed by an object to be detected.

Since the operation of identifying the tissue by the autofluorescence, such as the real-time detection operation of parathyroid gland, needs to be performed under the irradiation of an operation shadowless lamp (full spectrum with high brightness), the light intensity of stray light is relatively large, the light energy of autofluorescence is low, and the optical system is required to have enough light precision and also has a large enough measurement range.

Therefore, although parathyroid gland detection devices are already on the market at present, the parathyroid gland detection devices are not clinically accepted at present, and effective distinction between laser and surgical stray light and fluorescence cannot be realized, and the sufficient optical resolution and the large optical detection range are ensured.

Therefore, in order to solve the above-mentioned problems, there is a need for an apparatus for detecting an auto-fluorescent tissue, such as a parathyroid gland detection apparatus, which can effectively filter stray light, and can improve the parathyroid gland detection recognition rate by combining with algorithms such as laser signal modulation and demodulation, so as to clearly distinguish parathyroid gland from peripheral tissues such as thyroid gland, fat, etc.

Disclosure of Invention

The utility model provides a detection device for an autofluorescence tissue. The specific contents are as follows.

According to one aspect of the present utility model, there is provided a detection device of an autofluorescent tissue, the detection device comprising an optical system comprising the following optical elements: a laser light source for emitting modulated laser light; a light source side lens for collimating laser light emitted from the laser light source; a fiber side lens for collimating fluorescence returned after excitation of the laser; an optical fiber for transmitting laser light to the distal end on the laser excitation light path and transmitting fluorescence light to the proximal end on the fluorescence receiving light path; a photoelectric sensor for sensing fluorescent signal of passback, its characterized in that: the optical system further comprises a fluorescence filter used for filtering stray light, and the fluorescence filter is positioned between the light source side lens and the optical fiber side lens and used for filtering the stray light entering the receiving end face of the photoelectric sensor.

Preferably, the optical system has a linear optical path, and the linear optical paths are sequentially arranged along the optical axis from the proximal side to the distal side: the integrated laser light source, the photoelectric sensor, the light source side lens, the fluorescent filter, the optical fiber side lens and the optical fiber; the light source side lens forms a fluorescence receiving end lens and is used for focusing fluorescence signals filtered by the fluorescence filter to the photoelectric sensor.

Preferably, the optical system has an L-shaped optical path including a dichroic mirror, wherein the L-shaped optical path includes a laser excitation optical path and a fluorescence receiving optical path, which are perpendicular to each other; wherein, the laser excitation light is arranged from near side to far side in proper order on the road: a laser light source, a laser filter, and a dichroic mirror; the fluorescence receiving light paths are sequentially arranged from the near side to the far side: the photoelectric sensor, the sensor side lens, the fluorescent filter, the dichroic mirror, the optical fiber side lens and the optical fiber, wherein the sensor side lens forms a fluorescent receiving end lens; the included angle between the laser filter and the fluorescent filter is 90 degrees, and the included angle between the dichroic mirror and the laser filter and the fluorescent filter is 45 degrees.

Preferably, the optical system has a dual fiber optical path including a laser excitation optical path and a fluorescence reception optical path; wherein, the optical element that arranges in proper order from near side to distal side on the laser excitation light road includes: the device comprises a laser light source, a light source side lens, a laser filter, an optical fiber side lens and an optical fiber; the optical elements sequentially arranged from the near side to the far side on the fluorescence receiving light path comprise: the photoelectric sensor is positioned at the focal position of the sensor side lens, the dichroic mirror is arranged at an angle of 45 degrees with the optical axis, and the sensor side lens forms a fluorescence receiving end lens.

Preferably, the optical system has a diaphragm, which is arranged adjacent to the fluorescence receiving end of the photosensor.

Preferably, the diaphragm is located at the focal point of the fluorescence receiving end lens.

Preferably, the optical system is provided with one or more light absorbing means at a position parallel to the optical axis and between the light source side lens and the optical fiber side lens.

Preferably, the optical fiber is a single optical fiber.

Preferably, the laser light source has a laser filter cover.

Preferably, the fluorescence filter is a bandpass filter having an OD value of 6 or higher.

Preferably, the light absorbing means is a light absorbing cloth, a light absorbing plate, a light absorbing film or a light absorbing cavity.

Preferably, the autofluorescent tissue is parathyroid.

Preferably, the optical system further comprises a probe lens for focusing the laser transmitted by the optical fiber to the tissue to be measured and focusing a fluorescence signal generated by the laser excitation of the self-fluorescence tissue and transmitting the fluorescence signal to the optical fiber.

The detection device for self-fluorescent tissue according to the present utility model overcomes the aforementioned problems of the prior art. The detection device for the self-fluorescence tissue can improve the effective utilization rate of laser, improve the laser density and greatly improve the detection recognition rate of the self-fluorescence tissue; the weak fluorescent signal can be detected rapidly, and the effect of the background light of the operation environment is avoided; the disposable sterilizing consumable design is used, so that the risk of cross infection is reduced to the maximum extent in clinical use, and the disposable sterilizing consumable design is convenient, sanitary and high in economic benefit.

Drawings

Fig. 1 is a schematic diagram of the operation of the parathyroid detection apparatus of the present utility model.

Fig. 2 is a schematic view of a parathyroid detection device of the present utility model.

Fig. 3 is a schematic view of a linear optical system according to an embodiment of the present utility model.

Fig. 4 is a schematic view of an L-shaped optical system according to an embodiment of the present utility model.

Fig. 5 is a schematic diagram of a dual fiber optical path optical system according to an embodiment of the present utility model.

Fig. 6 is a schematic view of a linear optical system according to a preferred embodiment of the present utility model.

Fig. 7 is a schematic view of an L-shaped optical system according to a preferred embodiment of the present utility model.

Fig. 8 is a schematic diagram of a dual fiber optical path optical system according to a preferred embodiment of the present utility model.

Fig. 9-10 are schematic diagrams of optical systems with light absorbing devices according to preferred embodiments of the present utility model.

The reference numerals in the drawings respectively indicate: 1-a laser light source; 2-a light source side lens; 3. 3' -optical fiber side lens; 4. 4' -optical fiber; 5-a probe lens; 6-a photoelectric sensor; 7-a laser filter; 8-a dichroic mirror; 9-a fluorescent filter; 10-sensor side lenses; 11-diaphragm; 20-light absorbing means; 100-probe; 101-a probe lens; 200-handle; 300-an external fiber optic cable; 400-host computer; 401-cassette; 402-an inner fiber optic cable; 403-a laser emitting unit; 404-a fluorescence detection unit; 405-a controller; 406-HMI human-machine interface; 407-a wireless device; 408-a power supply system; 409-battery; 500-power adapter.

Detailed Description

The technical solution of the present utility model will be further described by way of specific embodiments with reference to the accompanying drawings, however, it will be understood by those skilled in the art that the present utility model is not limited to these specific embodiments. Other ways of implementing the utility model will occur to those skilled in the art on the basis of the preferred embodiments, which ways likewise fall within the scope of the utility model.

The term "direction" and "position" in the present utility model should be understood as a relative direction and a relative position, not an absolute direction and a relative position.

The parathyroid detection device provided by the utility model has the advantages that the fluorescent filter and the diaphragm are arranged beside the sensor side lens, so that irrelevant fluorescent stray light can be eliminated, the signal interference of the stray light is reduced, the parathyroid detection recognition rate is improved, and an operator can obviously distinguish parathyroid from peripheral tissues such as thyroid gland, fat and the like.

The parathyroid detection device in accordance with the present utility model is described in detail below with reference to FIGS. 1-10. It will be understood by those skilled in the art that the term proximal end, proximal, refers herein to the end or direction closer to the operator and away from the tissue under test when the device is operated, and the term distal end, distal, refers to the end or direction farther from the operator and closer to the tissue under test when the device is operated.

First, the working principle of the parathyroid detection device in the present utility model will be described. As shown in fig. 1, an operator sends an operation instruction to a control system through an HMI human-machine interface, the control system sends a modulation signal to a laser system to perform laser modulation after receiving the instruction, and a laser source emits modulated laser. The laser is irradiated on the human tissue including the parathyroid gland, and the parathyroid gland is excited by the laser to generate fluorescence. After the fluorescence is received, the control system carries out signal modulation such as phase-locking amplification and the like on the received fluorescence according to the set reference signal. Finally, the control system presents the detection result to the operator in an intuitive form through the HMI human-machine interface.

Fig. 2 shows a schematic view of the parathyroid detection apparatus of the present utility model. The parathyroid detection device includes a probe 100, a handpiece 200, an external fiber optic cable 300, a host 400, and a power adapter 500.

The probe lens 5 is arranged at the tail end of the probe 100, and can focus the emitted laser onto the tissue to be tested, and focus the fluorescent signal generated by the excitation of parathyroid gland laser and transmit the fluorescent signal to the optical fiber 4. The optical fiber 4 is responsible for transmitting the emitted laser light and the returned fluorescence light, and includes an external optical fiber cable 300 located outside the host of the parathyroid detection device and an internal optical fiber cable 402 located inside the host.

The handle 200 is intended to be held by an operator during operation of the device to place the probe 100 in position.

As previously described, the external fiber optic cable 300 is the portion of the optical fiber 4 that is located outside the host of the parathyroid detection device.

The host 400 includes a cassette 401, an internal fiber optic cable 402, a laser light emitting unit 403, a fluorescence detecting unit 404, a controller 405, an HMI human-machine interface 406, a wireless device 407, a power supply system 408, and a battery 409. The cassette 401 includes main components of the optical system of the parathyroid detection device, such as a laser light source 1, a light source side lens 2, a laser filter 7, a fiber side lens 3, a photosensor 6, and the like. As described below, the optical elements included in the cassette 401 are different depending on the optical path design of the optical system.

The power supply supplies power to the host 400 through the power adapter 500.

The operator of the parathyroid detection device sends an operating command to the controller 405 via the HMI human-machine interface 406 or the wireless device 407, whereupon the controller 405 sends a modulated signal. The HMI human-machine interface 405 may be a display screen display, or may be an expression form such as an audible and visual alarm, and various efficient recognition modes help an operator to quickly locate the parathyroid gland. The battery 409 can power the device in the absence of external power to enable the parathyroid detection device to accommodate a wide variety of complex and diverse environments. The distal end of the inner fiber optic cable 402 is directly coupled to the outer fiber optic cable 300 by a living connection, and the proximal end of the inner fiber optic cable 402 is connected to the cassette 401. The external fiber optic cable 300 may be movably coupled to the internal fiber optic cable 402 by a threaded swivel connection or a plug-in connection, or any other manner as will occur to those of skill in the art. This arrangement enables the cassette 401 to be placed at any position within the host 400, thereby making the structure of the host 400 more compact. The distal end of the outer fiber optic cable 300 is connected through the handpiece 200 to the probe lens 5, while the proximal end is connected to the inner fiber optic cable 402. The probe 100, the handle 200 and the external optical fiber cable 300 are fixedly connected, so that the probe can be replaced as a whole consumable, disposable sterile use is realized, and the operation efficiency and safety are improved.

Specific embodiments of the optical system of the parathyroid detection device in accordance with the present utility model are described below with reference to FIGS. 3-10, respectively. Wherein fig. 3-5 show a first embodiment of the optical system of the parathyroid detection device of the present utility model using a fluorescence filter 9 to filter out stray light, particularly stray light reflected from the proximal end of the optical fiber 4 of the parathyroid detection device. Fig. 6-8 show a second embodiment of the optical system of the parathyroid detection device of the present utility model which adds a diaphragm 11 to enhance stray light filtering. Fig. 9-10 show a third embodiment of the optical system of the parathyroid detection device of the present utility model in which a light absorbing means is used to further filter out stray light, particularly stray light resulting from repeated reflection, refraction by the dichroic mirror 8.

First embodiment

Example 1

Referring to fig. 3, there is a schematic view of a linear optical system according to example 1 of the first embodiment of the present utility model. In this embodiment 1, on the optical axis of the linear optical system, from the far side to the near side, there are arranged in order: the laser light source 1, the photoelectric sensor 6, the light source side lens 2, the fluorescence filter 9, the optical fiber side lens 3, the optical fiber 4 and the probe lens 5 are integrated together. The laser light source 1 is placed at the focal point of the light source side lens 2, and the proximal end of the optical fiber 4 is located at the focal point position of the optical fiber side lens 3.

In this embodiment, the laser light source 1 emits laser light, which is collimated by the light source side lens 2, and the collimated laser light is focused to the proximal end of the optical fiber 4 by the optical fiber side lens 3. Here, the vast majority of the laser light entering the optical fiber 4 is transmitted towards the distal end of the optical fiber 4, while a small portion is reflected proximally by the proximal end of the optical fiber 4 and becomes unwanted stray light. The laser light is transmitted to the probe lens 5 via the optical fiber 4. The laser is focused by the probe lens 5 to irradiate the tissue to be measured. Parathyroid glands in tissues to be detected generate fluorescence with peak value between 820 and 830nm wavelength under the excitation of laser. The excited fluorescence is received by the probe lens 5 and focused onto the distal end of the optical fiber 4. The fluorescence is transmitted to the optical fiber side lens 3 through the optical fiber 4. The fluorescence is collimated by the optical fiber side lens 3, and the collimated fluorescence filters out unwanted stray light of wavelength through the fluorescence filter 9, especially stray light reflected from the proximal end of the optical fiber 4 of the parathyroid gland detection device, and then is focused by the light source side lens 2 to the photoelectric sensor 6 (i.e., the light source side lens 2 also constitutes a fluorescence receiving end lens), and the photoelectric sensor 6 receives the fluorescence signal and transmits to the control system for modulation and analysis.

Example 2

Referring to fig. 4, there is a schematic view of an L-shaped optical system of example 2 according to the first embodiment of the present utility model. In this embodiment, the L-shaped optical system has two mutually perpendicular optical axes, an X-axis in the horizontal direction and a Y-axis in the vertical direction, respectively. The photoelectric sensor 6, the sensor-side lens 10, the fluorescence filter 9, the dichroic mirror 8, the optical fiber-side lens 3, the optical fiber 4, and the probe lens 5 are arranged in this order from the near side to the far side on the X axis, and the photoelectric sensor 6 is located at the focal position of the sensor-side lens 10. The sensor-side lens 10 constitutes a fluorescence receiving-end lens. A laser light source 1, a light source side lens 2, a laser filter 7, and a dichroic mirror 8 are arranged in order from the near side to the far side on the Y axis. Wherein the laser light source 1 is located at the focal position of the light source side lens 2, and the proximal end of the optical fiber 4 is located at the focal position of the optical fiber side lens 3. The included angle between the laser filter 7 and the fluorescent filter 9 is 90 degrees. As shown in fig. 4, the dichroic mirror 8 is placed at the intersection position of the two optical axes of the X axis and the Y axis, between the laser filter 7 and the fluorescent filter 9, and forms an angle of 45 degrees with both filters.

The optical path of the L-type optical system of this embodiment 2 is divided into a laser excitation optical path and a fluorescence receiving optical path. The laser excitation light path refers to a light path in which laser light is transmitted from the laser light source 1 to the tissue to be measured, and the fluorescence receiving light path refers to a light path in which fluorescence excited by the laser light is transmitted from the tissue to be measured to the photosensor 6.

The laser excitation light path of the optical path of the L-shaped optical system is as follows: the laser light source 1 emits laser light, and the laser light is collimated by the light source side lens 2. The laser filters out stray light of other wavelengths through the laser filter 7. The dichroic mirror 8 has a characteristic of refracting in the laser light band and transmitting in the fluorescence band, and thus the laser light is focused to the proximal end of the optical fiber 4 through the optical fiber side lens 3 after being refracted by the dichroic mirror 8. Here, the vast majority of the laser light entering the optical fiber 4 is transmitted towards the distal end of the optical fiber 4, while a small portion is reflected proximally by the proximal end of the optical fiber 4 and becomes unwanted stray light. The laser light is transmitted by the optical fiber 4 and then emitted from the distal end of the optical fiber 4. The emitted laser is focused on the human tissue to be measured by the probe lens 5.

The fluorescence receiving light path of the optical path of the L-shaped optical system is as follows: the parathyroid gland in the human tissue is excited by the laser to generate a fluorescence signal, and the fluorescence signal is focused to the distal end of the optical fiber 4 by the probe lens 5. The fluorescent signal is transmitted by the optical fiber 4 and output from the proximal end of the optical fiber 4. The fluorescent signal output from the optical fiber 4 is collimated by the optical fiber side lens 3, and as described above, the dichroic mirror 8 has a characteristic of refracting in the laser band and transmitting in the fluorescent band, and thus the fluorescent signal collimated by the optical fiber side lens 3 is transmitted by the dichroic mirror 8. The fluorescence signal is filtered by the fluorescence filter 9 to remove stray light with other wavelengths, and finally is focused to the photoelectric sensor 6 by the sensor side lens 10, and the photoelectric sensor 6 receives the fluorescence signal and transmits the fluorescence signal to the control system for modulation and analysis.

In the above embodiments 1, 2, although the present embodiment has been described above in terms of providing the probe lens 5, the probe lens 5 is not an essential component and may be omitted. However, in the technical solution provided with the probe lens 5, the probe lens 5 can transmit the laser light to the deep tissue more intensively, so that the detection effect is better.

Example 3

Referring to fig. 5, there is a schematic diagram of a dual fiber optical path optical system according to example 3 of the first embodiment of the present utility model. In this embodiment, the dual fiber optical path optical system has two optical axes. The photoelectric sensor 6, the sensor side lens 10, the fluorescent filter 9, the dichroic mirror 8, the optical fiber side lens 3 and the optical fiber 4 are sequentially arranged on the first optical axis from the near side to the far side, the photoelectric sensor 6 is positioned at the focal position of the sensor side lens 10, and the dichroic mirror 8 is arranged at an angle of 45 degrees with the optical axis. The proximal end of the optical fiber 4 is located at the focal position of the optical fiber side lens 3. The sensor-side lens 10 constitutes a fluorescence receiving-end lens. Each optical element on the first optical axis constitutes a fluorescence receiving optical path. A laser light source 1, a light source side lens 2, a laser filter 7, an optical fiber side lens 3', and an optical fiber 4' are arranged in this order from the near side to the far side on the second optical axis. Wherein the laser light source 1 is positioned at the focal position of the light source side lens 2, and the proximal end of the optical fiber 4 'is positioned at the focal position of the optical fiber side lens 3'. Each optical element on the second optical axis forms a laser excitation light path.

The optical path of the dual fiber optical path optical system of this embodiment 3 is divided into a laser excitation optical path and a fluorescence receiving optical path. The laser excitation light path refers to a light path in which laser light is transmitted from the laser light source 1 to the tissue to be measured, and the fluorescence receiving light path refers to a light path in which fluorescence excited by the laser light is transmitted from the tissue to be measured to the photosensor 6.

The laser excitation light path of the optical path of the double-fiber light path optical system is as follows: the laser light source 1 emits laser light, and the laser light is collimated by the light source side lens 2. The laser filters out stray light with other wavelengths through the laser filter 7, and is focused to the proximal end of the optical fiber 4 'through the optical fiber side lens 3'. The laser is transmitted by the optical fiber 4', and then emitted from the distal end of the optical fiber 4' to be transmitted to the human tissue to be measured.

The fluorescence receiving light path of the optical path of the double-fiber light path optical system is as follows: the parathyroid gland in the human tissue is excited by the laser to generate a fluorescence signal, the fluorescence signal enters the distal end of the optical fiber 4, and meanwhile, the laser reflected by the human tissue also enters the distal end of the optical fiber 4. Both the fluorescent signal and the reflected laser light are transmitted by the optical fiber 4 and output from the proximal end of the optical fiber 4. The fluorescent signal output from the optical fiber 4 is collimated by the optical fiber side lens 3, and as described above, the dichroic mirror 8 has a characteristic of refracting in the laser band and transmitting in the fluorescent band, so that the fluorescent signal collimated by the optical fiber side lens 3 is transmitted by the dichroic mirror 8, and the laser light is refracted. The fluorescence signal is filtered by the fluorescence filter 9 to remove stray light with other wavelengths, and finally is focused to the photoelectric sensor 6 by the sensor side lens 10, and the photoelectric sensor 6 receives the fluorescence signal and transmits the fluorescence signal to the control system for modulation and analysis.

Second embodiment

As shown in the following table, the applicant conducted experiments comparing fluorescence signals when using and without using diaphragms. In the experiment, a 785nm laser emission module and a bandpass filter with an OD value of 6 are adopted. The experimental data obtained are presented in the following table.

TABLE 1 comparison of Single Filter with stop

The signal to noise ratio=20log (Vs/V _{Skin of a person} )

Wherein Vs is the voltage value measured somewhere from the fluorescent reagent, V _{Skin of a person} Is the voltage value measured on the skin.

In the experiment, the probe 100 is in front contact with the skin, the laser is directly irradiated on the skin, the laser irradiates on the human tissue in a simulated real state, and the laser is reflected to the signal intensity of the fluorescence receiving end to be regarded as noise floor. Table 1 is a comparison table of a single optical filter and a single optical filter with diaphragms added, and the table describes the values obtained by converting an optical signal received by a photoelectric sensor at a receiving end into a voltage signal and capturing and subtracting the voltage excited by the background by an oscilloscope, and also describes the values of signal to noise ratio. Where the voltage is in mV and the signal to noise ratio is in dB.

From the data in table 1, it can be seen that after the diaphragm is added to the single optical filter, the effect of measuring the fluorescent signal is obviously better than that of the single optical filter, and the signal-to-noise ratio is improved by about 12dB when the single optical filter is arranged.

Accordingly, in order to further remove stray light and improve the detection effect on the basis of example 1, example 2, and example 3 of the first embodiment, the applicant has further improved the optical system described above, and has provided a stop at a suitable position of the optical path to filter out stray light. Specifically, a diaphragm is provided on the optical axis of the linear optical system described in embodiment 1, a diaphragm is provided on the X-axis of the L-shaped optical system described in embodiment 2, and a diaphragm is provided on the first optical axis of embodiment 3. Since the diaphragm plays a limiting role on the light beam in the optical system, the size of the light beam or the field of view can be limited. Referring to fig. 6-8, the position of the diaphragm is arranged at the distal end of the photosensor 6, between the fluorescence receiving end lens and the photosensor 6, preferably the diaphragm is arranged at the focal point of the fluorescence receiving end lens. Those skilled in the art can design various forms of diaphragms according to actual needs, for example, edges of lenses, frames or specially arranged perforated screens can be arranged as diaphragms as required.

Third embodiment

On the basis of the above embodiments, a light absorbing device is arranged beside each lens and parallel to the main optical axis to absorb redundant stray light, especially stray light generated by repeated reflection and refraction of the dichroic mirror 8, so that interference of the stray light on fluorescent signals is reduced, and the detection precision of parathyroid glands is improved. For example, referring to fig. 9, on the basis of the optical system described in example 2 of the first embodiment, for example, a light absorbing device 20 may be provided in the vicinity of the dichroic mirror 8 on the aforementioned Y axis, that is, the light absorbing device 20 is positioned parallel to the aforementioned X axis and between the fluorescence receiving end lens and the optical fiber side lens 3, and in the vicinity of each lens. In order to enhance the light absorbing effect, more than one light absorbing means 20 may be provided, as shown in fig. 10, wherein two light absorbing means 20 are provided on the basis of the foregoing example of embodiment 3. The person skilled in the art can suitably select a suitable light absorbing means 20, such as a light absorbing cloth, a light absorbing plate, a light absorbing film, a light absorbing cavity, etc., having a high absorptivity, as required.

Various embodiments of the present utility model are described in detail above with respect to fig. 1-10. It is further preferable that the laser light source 1 may be provided with a laser filter cover to filter stray light with other wavelengths.

The OD value of the fluorescent filter 9 used in the above embodiments may be appropriately selected by those skilled in the art according to actual needs, and a bandpass filter having an OD value of 6 or higher is preferable.

In addition, the outer fiber optic cable 300 and the inner fiber optic cable 402 of the optical fibers 4,4' may employ conventional dual fibers, but are preferably single fibers. The single optical fiber has more advantages for the utility model, because the transmitting end face and the receiving end face of the single optical fiber are the same end face, the receiving end face can receive all the fluorescent signals reflected vertically, and the transmitting end face and the receiving end face of the optical fiber are coplanar and can be positioned at the focal position of the probe lens 5 at the same time, so that the laser density can be improved, and the parathyroid recognition rate is improved.

It will be appreciated by those skilled in the art that although the utility model has been described above with respect to parathyroid glands as specific examples of tissue to be tested, the utility model is applicable to the detection of any tissue capable of being excited by a laser to produce autofluorescent properties of fluorescence.

Industrial applicability

With the apparatus for detecting self-fluorescent tissue, especially parathyroid gland detection apparatus, according to various embodiments of the present utility model, an operation command is sent to the controller 405 through the HMI human-machine interface 406 or the wireless device 407, the controller 405 sends out a modulated signal, the laser light source 3 sends out a laser signal to irradiate the parathyroid gland waiting tissue, the excited fluorescent signal sends out a similar signal to be transmitted to the photoelectric sensor 6, and finally the controller 405 sends out a detection result through the HMI human-machine interface 406 or the wireless device 406 through FFT spectrum analysis.

The foregoing description of various embodiments of the utility model has been presented for the purpose of illustration and is not intended to be exhaustive or limited to the utility model in the form disclosed. Many alternatives and modifications of the present utility model will be apparent to those of ordinary skill in the art in light of the above teachings. Thus, while some alternative embodiments have been specifically described, those of ordinary skill in the art will understand or relatively easily develop other embodiments. The present utility model is intended to embrace all alternatives, modifications and variations of the present utility model described herein and other embodiments that fall within the spirit and scope of the utility model described above.

Claims

1. A detection device for self-fluorescent tissue, the detection device comprising an optical system comprising the following optical elements:

a laser light source (1) for emitting modulated laser light;

a light source side lens (2) for collimating laser light emitted from the laser light source (1);

a fiber side lens (3) for collimating fluorescence returned after excitation of the laser;

an optical fiber (4) for transmitting laser light to the distal end on the laser excitation light path and transmitting fluorescence light to the proximal end on the fluorescence receiving light path;

a photosensor (6) for sensing the returned fluorescent signal,

the method is characterized in that:

the optical system further comprises a fluorescence filter (9) for filtering stray light, wherein the fluorescence filter (9) is positioned between the light source side lens (2) and the optical fiber side lens (3) and is used for filtering the stray light entering the receiving end face of the photoelectric sensor (6).

2. The apparatus for detecting self-fluorescent tissue according to claim 1, wherein the optical system has a linear optical path in which optical elements arranged in order along the optical axis from the proximal side to the distal side include: the laser light source, the photoelectric sensor (6), the light source side lens (2), the fluorescent filter (9), the optical fiber side lens (3) and the optical fiber (4) are integrated into a whole;

the light source side lens (2) forms a fluorescence receiving end lens and is used for focusing fluorescence signals filtered by the fluorescence filter (9) to the photoelectric sensor (6).

3. The device for the detection of self-fluorescent tissue according to claim 1, characterized in that the optical system has an L-shaped optical path comprising a dichroic mirror (8), wherein the L-shaped optical path comprises a laser excitation optical path and a fluorescence reception optical path, which are perpendicular to each other;

wherein, the optical element that arranges in proper order from near side to distal side on the laser excitation light road includes: a laser light source (1), a laser filter (7) and a dichroic mirror (8);

the optical elements sequentially arranged from the near side to the far side on the fluorescence receiving light path comprise: the photoelectric sensor (6), a sensor side lens (10), a fluorescence filter (9), a dichroic mirror (8), an optical fiber side lens (3) and an optical fiber (4), wherein the sensor side lens (10) forms a fluorescence receiving end lens;

the included angle between the laser filter (7) and the fluorescent filter (9) is 90 degrees, and the included angle between the dichroic mirror (8) and the laser filter (7) and the fluorescent filter (9) is 45 degrees.

4. The apparatus for detecting self-fluorescent tissue according to claim 1, wherein the optical system has a dual fiber optical path including a laser excitation optical path and a fluorescence receiving optical path;

wherein, the optical element that arranges in proper order from near side to distal side on the laser excitation light road includes: a laser light source (1), a light source side lens (2), a laser filter (7), an optical fiber side lens (3 ') and an optical fiber (4');

the optical elements sequentially arranged from the near side to the far side on the fluorescence receiving light path comprise: the photoelectric sensor (6), the sensor side lens (10), the fluorescence filter (9), the dichroic mirror (8), the optical fiber side lens (3) and the optical fiber (4), wherein the photoelectric sensor (6) is positioned at the focal position of the sensor side lens (10), the dichroic mirror (8) and the optical axis are arranged at an angle of 45 degrees, and the sensor side lens (10) forms a fluorescence receiving end lens.

5. An auto-fluorescent tissue detection device according to any one of claims 2-4, characterized in that the optical system has a diaphragm between the fluorescence receiving end lens and the photosensor (6).

6. The apparatus for detecting self-fluorescent tissue according to claim 5, wherein the diaphragm is positioned at a focal point of the fluorescent receiving end lens.

7. An auto-fluorescent tissue detection device according to any of claims 2-4, characterized in that the optical system is provided with one or more light absorbing means (20) parallel to the optical axis and between the fluorescence receiving end lens and the fiber side lens (3).

8. The device for the detection of self-fluorescent tissue according to any one of claims 1 to 4, characterized in that the optical fiber (4) is a single optical fiber.

9. The device for the detection of self-fluorescent tissue according to any one of claims 1 to 4, characterized in that the laser light source (1) has a laser filter cover.

10. The self-fluorescent tissue detection device according to any one of claims 1 to 4, wherein the fluorescent filter (9) is a bandpass filter having an OD value of 6 or higher.

11. The device for detecting self-fluorescent tissue according to claim 7, wherein the light absorbing means (20) is a light absorbing cloth, a light absorbing plate, a light absorbing film or a light absorbing cavity.

12. The apparatus for detecting self-fluorescent tissue according to any one of claims 1 to 4, wherein the self-fluorescent tissue is parathyroid.

13. A device for the detection of self-fluorescent tissue according to any one of claims 1 to 3, characterized in that the optical system further comprises a probe lens (5) for focusing the laser light transmitted by the optical fiber (4, 4') to the tissue to be examined and for focusing the fluorescent signal generated by the excitation of the self-fluorescent tissue by the laser light and transmitting it to the optical fiber (4).