A parathyroid gland intraoperative identification device

Abstract

The invention discloses a parathyroid intraoperative identification device, comprising an excitation light unit, a calibration light unit, a signal acquisition unit and a data processing unit, wherein the excitation light emitted by the excitation light unit is transmitted to the tissue to be tested through a probe; the calibration light emitted by the calibration light unit is transmitted to the tissue to be tested through the probe; the signal acquisition unit collects a fluorescent signal I1 and a calibration light signal I2 emitted by the tissue to be tested; the data processing unit detects the intensity of the light source and determines whether the light source needs to be replaced, and at the same time, performs distance correction on the fluorescent signal I1 according to distance information, and determines whether the tissue to be tested is parathyroid tissue according to the corrected fluorescent signal; the invention has the advantages of performing distance correction on the fluorescent signal I1 to avoid detection errors caused by different distances between the probe and the tissue to be tested, detecting the intensity of the light source during the measurement process, avoiding the weakening of the fluorescent signal due to the decrease in the intensity of the excitation light source, thereby reducing the detection error.

Description

Technical Field

[0001] The present invention relates to the technical field of biomedical engineering, and more specifically to a parathyroid gland intraoperative identification device. Background Art

[0002] Thyroid cancer is the fastest-growing solid malignant tumor worldwide. Currently, surgery is the preferred treatment for thyroid cancer. Hypoparathyroidism is an important complication of thyroidectomy, which seriously affects the patient's quality of life and becomes the main factor causing medical disputes. Therefore, effective preservation of parathyroid glands during surgery is still a difficult problem for thyroid surgeons. At present, the identification of parathyroid glands mainly relies on doctors' experience through naked eye identification, which is subject to subjective errors. In many cases, it is difficult for doctors to judge whether the tissue is parathyroid gland with the naked eye. At this time, intraoperative frozen biopsy is needed to identify the parathyroid glands, but this method still has shortcomings such as parathyroid gland damage, increased costs, the need for related technical equipment support, and long waiting time.

[0003] Research has found that the parathyroid glands contain specific fluorescent substances, whose fluorescence intensity is 2 to 12 times that of thyroid tissue. Near-infrared technology can identify parathyroid glands in real time during surgery, effectively improving the recognition rate of parathyroid glands during surgery, especially parathyroid glands that are not easily visible to the naked eye. For example, the real-time parathyroid gland recognition method based on near-infrared autofluorescence disclosed in Chinese Patent Publication No. CN110693458A. Currently, there are two main types of parathyroid gland recognition systems designed for this technology: fluorescence imaging and probe. Fluorescence imaging systems are easily affected by ambient light, and the operating room lights need to be turned off during surgery. In addition, the diameter of the parathyroid gland is generally only 3 to 6 mm, and it is difficult for surgeons to accurately locate the corresponding position of the parathyroid gland indicated by the fluorescent image. The probe detection system can directly determine the suspected parathyroid tissue that has been located, and is not sensitive to ambient light, but will be affected by the shadowless lamp that overlaps with the fluorescence band, requiring doctors to turn off or move the shadowless lamp before use. Since fiber optic probes contact tissues for measurement, there are risks of allergies and infections, so non-contact measurement probes are mostly used. However, the distance of non-contact measurement probes will reduce the accuracy and repeatability of measurement results. At the same time, different intensities of excitation light sources will also cause different intensities of fluorescent signals, resulting in detection errors. Summary of the invention

[0004] The technical problem to be solved by the present invention is that the distance between the probes of the prior art parathyroid surgery identification device will reduce the accuracy and repeatability of the measurement results, and the different intensities of the excitation light source will also cause different intensities of the fluorescent signal, resulting in detection errors.

[0005] The present invention solves the above technical problems through the following technical means: a parathyroid intraoperative identification device, comprising an excitation light unit, a calibration light unit, a signal acquisition unit and a data processing unit, wherein the excitation light emitted by the excitation light unit is transmitted to the tissue to be tested through a probe, and excites the tissue to be tested to emit fluorescence; the calibration light emitted by the calibration light unit is transmitted to the tissue to be tested through the probe; the signal acquisition unit collects the fluorescence signal I1 and the calibration light signal I2 emitted by the tissue to be tested, and transmits the real-time data to the data processing unit; when the data processing unit detects that the signal intensity I3 of the excitation light emitted by the excitation light unit is greater than a set value B, the light source detection is passed, otherwise, a prompt to replace the light source is given, and in addition The intensity of the fluorescence signal I1 is negatively correlated with the distance d1 between the probe and the tissue to be measured, and the intensity of the calibration light signal I2 is negatively correlated with the distance d2 between the probe and the tissue to be measured, d2=f2(I2), f2 is the function of d2 with respect to I2, since d1=d2, according to the distance information, the fluorescence signal I1 is distance corrected by the formula I=f1(I1,d1)=f1(I1,d2)=f1(I1,f2(I2)) to obtain the corrected fluorescence signal I, wherein f1 is the function of I with respect to I1 and d1; when I≥A, the tissue to be measured is judged to be parathyroid tissue, and when I<A, the tissue to be measured is judged not to be parathyroid tissue, and A is the reference value.

[0006] The present invention performs distance correction on the fluorescent signal I1 according to the distance information, thereby avoiding detection errors caused by different distances between the probe and the tissue to be measured, thereby avoiding the problem of reduced accuracy and repeatability of the measurement results caused by the distance of the probe. In addition, the light source intensity is detected during the measurement process. When the signal intensity I3 of the excitation light emitted by the excitation light unit is less than the set value, a prompt is given to replace the light source to avoid weakening of the fluorescent signal due to a decrease in the light intensity of the excitation light source, thereby reducing detection errors and improving detection accuracy and stability.

[0007] Furthermore, the excitation light unit includes an excitation light source, a first filter and a first coupling optical path. The excitation light source is opposite to the first filter, and the first filter is opposite to the optical fiber entrance port of the first coupling optical path. The light emitted by the excitation light source is divided into two beams of light after passing through the filter and the first coupling optical path. One beam of light enters the excitation light calibration optical fiber, and the excitation light calibration optical fiber is connected to the signal acquisition unit. The other beam of light enters the excitation optical fiber and irradiates the tissue to be tested through the probe. The autofluorescence returned from the tissue to be tested is transmitted to the signal acquisition unit via the fluorescence collection optical fiber.

[0008] Furthermore, the calibration light unit includes a calibration light source, a second filter and a second coupling optical path. The calibration light source is opposite to the second filter, and the second filter is opposite to the optical fiber entrance port of the second coupling optical path. The light emitted by the calibration light source passes through the second filter and the second coupling optical path, is coupled into the calibration optical fiber, and is irradiated to the tissue to be measured through the probe. The reflected light returned from the tissue to be measured is transmitted to the signal acquisition unit through the calibration light collection optical fiber.

[0009] Furthermore, the signal acquisition unit includes a fluorescence signal acquisition unit and a calibration signal acquisition unit. The fluorescence signal acquisition unit acquires the fluorescence signal emitted by the excitation light unit when stimulating the tissue to be tested, and the calibration signal acquisition unit acquires the reflected light returned after the calibration light unit irradiates the tissue to be tested.

[0010] Furthermore, the fluorescence signal acquisition unit includes a third filter, a first photodetector and a third coupling optical path, the fluorescence collection optical fiber is connected to the optical fiber input port of the third coupling optical path, the optical fiber output port of the third coupling optical path is facing the third filter, and the third filter is facing the first photodetector.

[0011] Furthermore, the calibration signal acquisition unit includes a fourth filter, a second photodetector and a fourth coupling optical path, the excitation light calibration optical fiber and the calibration light collection optical fiber are both connected to the optical fiber input port of the fourth coupling optical path, the optical fiber output port of the fourth coupling optical path is facing the fourth filter, and the fourth filter is facing the second photodetector.

[0012] Furthermore, the signal acquisition unit includes a filter wheel and a third photodetector, the filter wheel is facing the third photodetector, and when monitoring the light source, the filter wheel is in state a, and the light transmitted by the excitation light calibration optical fiber enters the third photodetector through the filter wheel; when collecting fluorescence signals, the filter wheel is first in state b, and the light transmitted by the fluorescence collection optical fiber enters the third photodetector through the filter wheel, and then the filter wheel is converted to state c, and the light transmitted by the calibration light collection optical fiber enters the third photodetector through the filter wheel.

[0013] Furthermore, the signal acquisition unit includes a specific filter and a fourth photodetector, the specific filter is opposite to the fourth photodetector, the specific filter has different transmittances for the excitation light, the calibration light and the fluorescence signal, and the light transmitted by the excitation light calibration optical fiber, the light transmitted by the fluorescence collection optical fiber and the light transmitted by the calibration light collection optical fiber all pass through the specific filter and enter the fourth photodetector.

[0014] Furthermore, the fourth photodetector is a spectrometer.

[0015] Furthermore, the parathyroid intraoperative identification device also includes a data display unit, which is connected to the data processing unit, and the data display unit displays the data collected by the signal acquisition unit, prompt information for replacing the light source, and the detection result of the tissue to be tested.

[0016] The advantages of the present invention are as follows: the present invention performs distance correction on the fluorescent signal I1 according to the distance information, thereby avoiding detection errors caused by different distances between the probe and the tissue to be measured, thereby avoiding the problem of reduced accuracy and repeatability of the measurement results caused by the distance of the probe. In addition, the light source intensity is detected during the measurement process. When the signal intensity I3 of the excitation light emitted by the excitation light unit is less than the set value, a prompt is given to replace the light source, thereby avoiding the weakening of the fluorescent signal due to the decrease in the light intensity of the excitation light source, thereby reducing the detection error and improving the detection accuracy and stability. BRIEF DESCRIPTION OF THE DRAWINGS

[0017] Figure 1 This is a structural block diagram of a parathyroid gland intraoperative identification device disclosed in Embodiment 1 of the present invention;

[0018] Figure 2 This is a schematic diagram of the structure of a transmission unit in a parathyroid intraoperative identification device disclosed in Embodiment 1 of the present invention;

[0019] Figure 3 This is a schematic diagram of a parathyroid intraoperative identification device disclosed in Example 1 of the present invention. DETAILED DESCRIPTION

[0020] In order to make the purpose, technical solution and advantages of the embodiments of the present invention clearer, the technical solution in the embodiments of the present invention will be clearly and completely described below in combination with the embodiments of the present invention. Obviously, the described embodiments are part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the present invention.

[0021] Example 1

[0022] like Figure 1 As shown, a parathyroid gland intraoperative identification device includes an excitation light unit 1, a calibration light unit 2, a signal acquisition unit, a data processing unit 7 and a data display unit 8. Figure 2 As shown, in this embodiment, signal transmission between each unit is realized through a transmission unit 5, and the transmission unit 5 is used to transmit excitation light, calibration light and fluorescence signal, and includes an excitation optical fiber 51, a calibration optical fiber 52, a fluorescence collection optical fiber 53, a calibration light collection optical fiber 54, a probe 55 and an excitation light calibration optical fiber 56.

[0023] like Figure 3As shown, the excitation light emitted by the excitation light unit 1 is transmitted to the tissue to be tested 6 through the probe 55, and excites the tissue to be tested 6 to emit fluorescence. The excitation light unit 1 includes an excitation light source 11, a first filter 12 and a first coupling optical path 13. The excitation light source 11 is opposite to the first filter 12, and the first filter 12 is opposite to the optical fiber entrance port of the first coupling optical path 13.

[0024] The calibration light emitted by the calibration light unit 2 is transmitted to the tissue to be tested 6 through the probe 55. The calibration light unit 2 includes a calibration light source 21, a second filter 22 and a second coupling optical path 23. The calibration light source 21 is opposite to the second filter 22, and the second filter 22 is opposite to the optical fiber entrance port of the second coupling optical path 23.

[0025] The signal acquisition unit collects the fluorescence signal I1 and the calibration light signal I2 emitted by the tissue to be tested 6, and transmits the real-time data to the data processing unit 7. The signal acquisition unit includes a fluorescence signal acquisition unit 3 and a calibration signal acquisition unit 4. The fluorescence signal acquisition unit 3 collects the fluorescence signal emitted by the tissue to be tested 6 when the excitation light unit 1 excites the tissue to be tested, and the calibration signal acquisition unit 4 collects the reflected light returned after the calibration light unit 2 irradiates the tissue to be tested 6. The fluorescence signal acquisition unit 3 includes a third filter 31, a first photodetector 32 and a third coupling optical path 33. The fluorescence collection optical fiber 53 is connected to the optical fiber incident port of the third coupling optical path 33, and the optical fiber outlet port of the third coupling optical path 33 is opposite to the third filter 31, and the third filter 31 is opposite to the first photodetector 32. The calibration signal acquisition unit 4 includes a fourth filter 41, a second photodetector 42 and a fourth coupling optical path 43. The excitation light calibration optical fiber 56 and the calibration light collection optical fiber 54 are both connected to the optical fiber input port of the fourth coupling optical path 43. The optical fiber output port of the fourth coupling optical path 43 is opposite to the fourth filter 41, and the fourth filter 41 is opposite to the second photodetector 42.

[0026] The specific principle process of the present invention is as follows: the light emitted by the excitation light source 11 is divided into two beams after passing through the filter and the first coupling optical path 13. One beam of light enters the excitation light calibration optical fiber 56, and the excitation light calibration optical fiber 56 is connected to the optical fiber incident port of the fourth coupling optical path 43 in the calibration signal acquisition unit 4, so that the calibration signal acquisition unit 4 acquires the excitation light signal. The other beam of light enters the excitation optical fiber 51 and irradiates the tissue to be tested 6 through the probe 55. The autofluorescence returned from the tissue to be tested 6 is transmitted to the optical fiber incident port of the third coupling optical path 33 in the fluorescence signal acquisition unit 3 through the fluorescence collection optical fiber 53, so that the fluorescence signal acquisition unit 3 acquires the fluorescence signal emitted by the tissue to be tested 6. The light emitted by the calibration light source 21 is coupled into the calibration optical fiber 52 after passing through the second filter 22 and the second coupling optical path 23, and irradiates the tissue to be tested 6 through the probe 55. The reflected light returned from the tissue to be tested 6 is transmitted to the optical fiber incident port of the fourth coupling optical path 43 of the calibration signal acquisition unit 4 through the calibration light collection optical fiber 54, so that the calibration signal acquisition unit 4 acquires the calibration light.

[0027] Due to the loss of the light source, as the use time increases, the light intensity of the excitation light source 11 decreases, which will cause the fluorescence signal to weaken and affect the accuracy of the measurement. Therefore, it is necessary to monitor the intensity of the excitation light source 11. When the data processing unit 7 detects that the signal intensity I3 of the excitation light emitted by the excitation light unit 1 is ≥ 90% of the initial light intensity of the light source, the light source detection passes and the next step can be performed; when I3 < 90% of the initial light intensity of the light source, it is prompted that the light source needs to be replaced. In addition, the intensity of the fluorescent signal I1 received by the fluorescent signal acquisition unit 3 is negatively correlated with the distance d1 between the probe 55 and the tissue to be measured 6, and the intensity of I1 is also related to the fluorescence intensity emitted by the tissue to be measured 6. The intensity of the calibration light signal I2 received by the calibration signal acquisition unit 4 is negatively correlated with the distance d2 between the probe 55 and the tissue to be measured 6, and has nothing to do with the fluorescence intensity of the tissue to be measured 6, so d2 = f2 (I2), f2 is a function of d2 with respect to I2, when the detection distance ≤ 4mm, d2 = α / I2, α is determined by the system performance, and is determined by measuring I2 under the condition of a known distance d2. Since d1=d2, according to the distance information, the distance correction of the fluorescence signal I1 is performed by the formula I=f1(I1,d1)=f1(I1,d2)=f1(I1,f2(I2)), and the corrected fluorescence signal I is obtained, wherein f1 is the function of I with respect to I1 and d1. When the detection distance is ≤4mm, I=βI1 / d1=βI1 / d2=βI1I2 / α, and β is determined by the system performance. When the fluorescence intensity I is known, it is determined by measuring I1. When I≥A, it is judged that the tissue 6 to be tested is parathyroid tissue. When I<A, it is judged that the tissue 6 to be tested is not parathyroid tissue. A is a reference value, which is related to the corresponding value of the detector. The reference value A is obtained by measuring the parathyroid standard phantom. The reference value A belongs to the relative light intensity value, and the range of A is between 500-1000. The addition of a distance measuring device will increase the volume of the probe, which will cause inconvenience to the operator. In addition, since the parathyroid gland is only 3-6mm, it cannot be guaranteed that the distance measuring device, the fluorescent probe and the parathyroid tissue to be measured maintain the same distance. In this distance correction method, the optical fiber required for calibration and the optical fiber required for fluorescence detection are integrated into the same probe, and the optical fiber core diameter is less than 1mm. The increase in the volume of the probe will not cause inconvenience to the operator, and it can ensure that the optical fiber required for calibration and the detection optical fiber maintain the same distance from the parathyroid tissue to be measured.

[0028] The data display unit 8 is connected to the data processing unit 7 , and the data display unit 8 displays the data collected by the signal collection unit, the prompt information for replacing the light source, and the detection result of the tissue to be tested 6 .

[0029] Through the above technical scheme, the present invention performs distance correction on the fluorescent signal I1 according to the distance information, thereby avoiding the detection error caused by the different distances between the probe 55 and the tissue 6 to be measured, thereby avoiding the problem of reduced accuracy and repeatability of the measurement results caused by the distance of the probe 55. In addition, the light source intensity is detected during the measurement process. When the signal intensity I3 of the excitation light emitted by the excitation light unit 1 is less than the set value, a prompt is given to replace the light source to avoid the weakening of the fluorescent signal due to the decrease in the light intensity of the excitation light source 11, thereby reducing the detection error and improving the detection accuracy and stability.

[0030] Example 2

[0031] The difference between Example 2 of the present invention and Example 1 is that the structure of the signal acquisition unit is different. In this embodiment, the signal acquisition unit includes a filter wheel and a third photodetector. The filter wheel is opposite to the third photodetector. When monitoring the light source, the filter wheel is in state a, and the light transmitted by the excitation light calibration optical fiber 56 enters the third photodetector through the filter wheel; when collecting fluorescence signals, the filter wheel is first in state b, and the light transmitted by the fluorescence collection optical fiber 53 enters the third photodetector through the filter wheel. Then the filter wheel is converted to state c, and the light transmitted by the calibration light collection optical fiber 54 enters the third photodetector through the filter wheel. The filter wheel is a filter that is driven to rotate by a rotating component. During the rotation, when the filter is facing the excitation light calibration optical fiber 56, it is in state a, and the part outside the area where the light source emitted by the excitation light calibration optical fiber 56 is located is in a blocked state. Similarly, during the rotation, when the filter is facing the fluorescence collection optical fiber 53, it is in state b, and the part outside the area where the light source emitted by the fluorescence collection optical fiber 53 is located is in a blocked state. Similarly, during the rotation, when the filter is facing the calibration light collection optical fiber 54, it is in state c, and the part outside the area where the light source emitted by the calibration light collection optical fiber 54 is located is in a blocked state.

[0032] Example 3

[0033] The difference between Example 3 of the present invention and Example 1 is that the structure of the signal acquisition unit is different. The signal acquisition unit in this embodiment includes a specific filter and a fourth photodetector. The specific filter is opposite to the fourth photodetector. The specific filter has different transmittances for the excitation light, the calibration light and the fluorescence signal, so that the fourth photodetector can collect three light beams at the same time without exceeding the range of the fourth photodetector. The light transmitted by the excitation light calibration optical fiber 56, the light transmitted by the fluorescence collection optical fiber 53 and the light transmitted by the calibration light collection optical fiber 54 all pass through the specific filter and enter the fourth photodetector. The fourth photodetector is a spectrometer.

[0034] The above embodiments are only used to illustrate the technical solutions of the present invention, rather than to limit the same. Although the present invention has been described in detail with reference to the aforementioned embodiments, those skilled in the art should understand that the technical solutions described in the aforementioned embodiments may still be modified, or some of the technical features may be replaced by equivalents. However, these modifications or replacements do not deviate the essence of the corresponding technical solutions from the spirit and scope of the technical solutions of the embodiments of the present invention.

Claims

1. A parathyroid gland intraoperative identification device, characterized in that: The invention comprises an excitation light unit, a calibration light unit, a signal acquisition unit and a data processing unit. The excitation light emitted by the excitation light unit is transmitted to the tissue to be tested through the probe, and excites the tissue to be tested to emit fluorescence. The calibration light emitted by the calibration light unit is transmitted to the tissue to be tested through the probe. The signal acquisition unit collects the fluorescence signal I1 and the calibration light signal I2 emitted by the tissue to be tested, and transmits the real-time data to the data processing unit. When the data processing unit detects that the signal intensity I3 of the excitation light emitted by the excitation light unit is greater than the set value B, the light source detection is passed. Otherwise, it is prompted to replace the light source. In addition, the intensity of the fluorescence signal I1 is related to the probe and the tissue to be tested. The intensity of the calibration light signal I2 is negatively correlated with the distance d1 between the probe and the tissue to be tested, d2=f2(I2), f2 is the function of d2 with respect to I2, since d1=d2, according to the distance information, the fluorescence signal I1 is distance-corrected by the formula I=f1(I1,d1)=f1(I1,d2)=f1(I1,f2(I2)), and the corrected fluorescence signal I is obtained, wherein f1 is the function of I with respect to I1 and d1; when I≥A, the tissue to be tested is judged to be parathyroid tissue, and when I<A, the tissue to be tested is judged not to be parathyroid tissue, and A is the reference value; The excitation light unit includes an excitation light source, a first filter and a first coupling light path, the excitation light source is directly opposite to the first filter, the first filter is directly opposite to the optical fiber incident port of the first coupling light path, the light emitted by the excitation light source is divided into two beams of light after passing through the filter and the first coupling light path, one beam of light enters the excitation light calibration optical fiber, the excitation light calibration optical fiber is connected to the signal acquisition unit, and the other beam of light enters the excitation optical fiber and irradiates the tissue to be tested through the probe, and the autofluorescence returned from the tissue to be tested is transmitted to the signal acquisition unit through the fluorescence collection optical fiber; The calibration light unit comprises a calibration light source, a second optical filter and a second coupling optical path, wherein the calibration light source is directly opposite to the second optical filter, and the second optical filter is directly opposite to the optical fiber incident port of the second coupling optical path, and the light emitted by the calibration light source is coupled into the calibration optical fiber after passing through the second optical filter and the second coupling optical path, and is irradiated to the tissue to be measured through the probe, and the reflected light returned from the tissue to be measured is transmitted to the signal acquisition unit through the calibration light collection optical fiber; The signal acquisition unit includes a fluorescence signal acquisition unit and a calibration signal acquisition unit. The fluorescence signal acquisition unit acquires the fluorescence signal emitted by the excitation light unit when stimulating the tissue to be tested, and the calibration signal acquisition unit acquires the reflected light returned after the calibration light unit irradiates the tissue to be tested.

2. A parathyroid gland intraoperative identification device according to claim 1, characterized in that: The fluorescence signal acquisition unit includes a third filter, a first photodetector and a third coupling optical path. The fluorescence collection optical fiber is connected to the optical fiber input port of the third coupling optical path. The optical fiber output port of the third coupling optical path faces the third filter, and the third filter faces the first photodetector.

3. A parathyroid gland intraoperative identification device according to claim 2, characterized in that: The calibration signal acquisition unit includes a fourth filter, a second photodetector and a fourth coupling optical path. The excitation light calibration optical fiber and the calibration light collection optical fiber are both connected to the optical fiber input port of the fourth coupling optical path. The optical fiber output port of the fourth coupling optical path is opposite to the fourth filter, and the fourth filter is opposite to the second photodetector.

4. The parathyroid gland intraoperative identification device according to claim 1, characterized in that: The signal acquisition unit includes a filter wheel and a third photodetector, the filter wheel is facing the third photodetector, when the light source is monitored, the filter wheel is in state a, and the light transmitted by the excitation light calibration optical fiber enters the third photodetector through the filter wheel; when the fluorescence signal is collected, the filter wheel is first in state b, and the light transmitted by the fluorescence collection optical fiber enters the third photodetector through the filter wheel, and then the filter wheel is converted to state c, and the light transmitted by the calibration light collection optical fiber enters the third photodetector through the filter wheel.

5. The parathyroid gland intraoperative identification device according to claim 1, characterized in that: The signal acquisition unit includes a specific filter and a fourth photodetector. The specific filter is opposite to the fourth photodetector. The specific filter has different transmittances for the excitation light, calibration light and fluorescence signal. The light transmitted by the excitation light calibration optical fiber, the light transmitted by the fluorescence collection optical fiber and the light transmitted by the calibration light collection optical fiber all pass through the specific filter and enter the fourth photodetector.

6. The parathyroid gland intraoperative identification device according to claim 5, characterized in that: The fourth photodetector is a spectrometer.

7. The parathyroid gland intraoperative identification device according to claim 1, characterized in that: It also includes a data display unit, which is connected to the data processing unit and displays the data collected by the signal acquisition unit, prompt information for replacing the light source, and the detection result of the tissue to be tested.

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