CN114886542A

CN114886542A - Cold and hot ablation system and control method thereof

Info

Publication number: CN114886542A
Application number: CN202210822941.8A
Authority: CN
Inventors: 王时; 熊飞; 肖剑; 韦文生; 杨晶晶; 黄乾富
Original assignee: Hygea Medical Technology Co Ltd
Current assignee: Hygea Medical Technology Co Ltd
Priority date: 2022-07-14
Filing date: 2022-07-14
Publication date: 2022-08-12
Anticipated expiration: 2042-07-14
Also published as: CN115486928A; CN114886542B

Abstract

The invention relates to a cold and hot ablation system and a control method thereof, relates to the technical field of ablation, and is used for meeting the control requirements of less working medium consumption flow and larger ice ball size. The cold and hot ablation system comprises a cold source, an ablation instrument and a valve mechanism, and the flow of the working medium in different stages and different positions is controlled, so that the flow of the consumed working medium and the size of the obtained ice hockey are controllable in the operation process of the system, the requirements of reducing the flow of the consumed working medium and increasing the size of the ice hockey can be met, different treatment strategies are adapted, and the optimal treatment time and treatment effect can be obtained.

Description

Cold and hot ablation system and control method thereof

Technical Field

The invention relates to the technical field of ablation, in particular to a cold and hot ablation system and a control method thereof.

Background

A thermal ablation system is a minimally invasive device that employs physiotherapy to treat tumors. In the freezing stage, cold working medium is supplied to the ablation instrument, so that the therapeutic end of the ablation instrument forms an ice ball, ice crystals are formed in tumor cell tissues, the tumor cells are damaged, and the low temperature simultaneously promotes the blood vessels to contract to form micro thrombus to trigger the tumor cells to die due to oxygen deficiency, thereby achieving the purpose of treatment.

According to the working principle in the treatment process, the cold and hot ablation system is very concerned about the working medium temperature of the treatment end of the ablation instrument in the operation process, and the commonly used means for adjusting the working medium temperature is to adjust the pressure of the treatment end of the ablation instrument. In practice, the size of the ice ball formed by the ablation apparatus in the treatment process is related to the flow of the working medium at different positions, so that the dual effects of less consumption of the working medium flow and larger size of the obtained ice ball can be achieved by controlling the flow of the working medium.

Disclosure of Invention

The invention provides a cold and hot ablation system and a control method thereof, which are used for meeting the control requirements of less working medium consumption flow and larger ice ball size.

The invention provides a cold and hot ablation system, comprising:

the cold source is provided with a total output side and a first output side connected with the total output side;

an ablation instrument coupled to the cold source, the ablation instrument having a first output side and a second output side; and

a valve mechanism for controlling the output flow of the cooling source and the ablation instrument;

adjusting the opening degree of the valve mechanism to enable the first output side of the cold source to output working media at a first flow rate, and the first output side of the ablation instrument to output working media at a second flow rate to pre-cool, wherein the second flow rate is greater than the first flow rate;

adjusting the opening degree of the valve mechanism to enable the first output side of the cold source to output working media at a third flow rate, and the second output side of the ablation instrument to output working media at a fourth flow rate to enable ice balls with preset sizes to be formed in the ablation instrument, wherein the fourth flow rate is larger than the third flow rate;

wherein the third flow rate is less than the first flow rate, and the fourth flow rate is greater than the second flow rate.

In one embodiment, the valve mechanism comprises:

a first valve disposed at a general output side of the cool source;

a phase separation valve disposed at a first output side of the cool source; and

a second valve disposed on a first output side of the ablation instrument;

and the first output side of the cold source can output working medium at a first flow rate by controlling the opening degree of one or more of the first valve, the phase separation valve and the second valve, and the first output side of the ablation instrument can output working medium at a second flow rate.

In one embodiment, the valve mechanism further comprises:

a third valve disposed on a second output side of the ablation instrument; and

a fourth valve disposed on a first supplemental tube connected to a second output side of the ablation instrument;

and the first output side of the cold source can output working medium at a third flow rate and the second output side of the ablation instrument can output working medium at a fourth flow rate by controlling the opening degree of one or more of the first valve, the phase separation valve, the second valve, the third valve and the fourth valve.

In one embodiment, the valve mechanism further comprises:

a fifth valve disposed on a second supplemental tube connected to the first input side of the ablation instrument; and

a sixth valve disposed on a third output side of the ablation instrument;

the first input side of the ablation instrument inputs treatment working medium at a fifth flow rate by adjusting the opening degree of one or more of the first valve, the fifth valve and the sixth valve, and the third output side of the ablation instrument outputs the treated working medium at a sixth flow rate;

wherein the sixth flow rate is greater than the fifth flow rate.

In one embodiment, further comprising a first storage mechanism and a second storage mechanism;

the first storage mechanism is respectively connected with the first output side of the cold source, the first output side of the ablation instrument and the first supplement pipe, and the first storage mechanism can respectively collect working media output by the first output side of the cold source and the working media output by the first output side of the ablation instrument or supplement the working media to the second output side of the ablation instrument;

the second storage mechanism is respectively connected with the second supplementing pipe and the cold source.

In one embodiment, further comprising a flow pump mechanism, the flow pump mechanism comprising:

a first flow pump located at a first output side of the cold source for obtaining a first flow rate and a third flow rate;

a second flow pump located at the first output side of the ablation instrument for obtaining the second flow;

a third flow pump located at a second output side of the ablation instrument for obtaining the fourth flow;

a fourth flow pump on a second supplemental tube connected to the first input side of the ablation instrument for obtaining a fifth flow; and

a fifth flow pump located at a third output side of the ablation instrument for obtaining a sixth flow.

The flow pump mechanism further comprises a cold source flow pump which is located on the total output side of the cold source and used for obtaining working medium consumption flow.

According to a second aspect of the present invention, there is provided a control method for a thermal ablation system, comprising the steps of:

the first output side of the control cooling source outputs working media with a first flow rate, and the first output side of the ablation instrument outputs working media with a second flow rate for precooling; wherein the second flow rate is greater than the first flow rate;

the first output side of the control refrigeration source outputs working medium with a third flow rate, and the second output side of the ablation instrument outputs working medium with a fourth flow rate, so that ice balls with preset sizes are formed in the ablation instrument; wherein the fourth flow rate is greater than the third flow rate;

the first flow rate is greater than the third flow rate and the fourth flow rate is greater than the second flow rate.

In one embodiment, the first output side of the cooling source is controlled to output working medium at a first flow rate by adjusting the opening degree of one or more of the first valve, the phase separation valve and the second valve, and the first output side of the ablation instrument outputs working medium at a second flow rate;

wherein the first valve is positioned at the total output side of the cold source;

the phase separation valve is positioned at the first output side of the cold source;

the second valve is located on a first output side of the ablation instrument.

In one embodiment, the first output side of the cooling source is controlled to output working medium at a third flow rate by adjusting the opening degree of one or more of the first valve, the phase separation valve, the second valve, the third valve and the fourth valve, and the second output side of the ablation instrument outputs working medium at a fourth flow rate;

the second valve is located on the first output side of the ablation instrument;

the third valve is positioned on the second output side of the ablation instrument;

the fourth valve is located on a first supplemental tube connected to the second output side of the ablation device.

In one embodiment, the method further comprises the following operation steps:

ice ball stabilization stage: controlling a first input side of the ablation instrument to input a treatment working medium at a fifth flow rate, and a third output side of the ablation instrument to output the treated working medium at a sixth flow rate, so that the size of an ice ball formed in the ablation instrument is maintained within a preset size range;

wherein the sixth flow rate is greater than the fifth flow rate.

In one embodiment, the first input side of the ablation apparatus is controlled to input the treatment working medium at a fifth flow rate by making the opening degrees of the phase separation valve, the second valve and the third valve zero, and the first input side of the ablation apparatus is controlled to output the treated working medium at a sixth flow rate by adjusting the opening degree of one or more of the first valve, the fifth valve and the sixth valve;

wherein the fifth valve is located on a second supplemental tube connected to the first input side of the ablation instrument;

the sixth valve is located on a third output side of the ablation instrument.

Compared with the prior art, the ice hockey therapeutic system has the advantages that the flow of the working medium consumed in the operation process of the system and the obtained ice hockey size are controllable by controlling the flow of the working medium at different stages and different positions, so that the requirements of reducing the flow of the consumed working medium and increasing the size of the ice hockey can be met, different therapeutic strategies are adapted, and the optimal therapeutic time and therapeutic effect can be obtained.

Drawings

The invention will be described in more detail hereinafter on the basis of embodiments and with reference to the accompanying drawings.

Fig. 1 is a schematic structural diagram of a thermal ablation system in an embodiment of the invention.

Reference numerals:

1-a first valve; 2-a second valve; 3-a third valve; 4-a fourth valve; 5-a fifth valve; 6-a sixth valve; 11-a phase separation valve;

100-a cold source; 110-a first cold source output pipe; 120-a second cold source output pipe; 101-cold source flow pump;

200-an ablation instrument; 210-a first ablation instrument output tube; 220-a second ablation instrument output tube; 230-efferent vessel of the third ablation apparatus; 231-fifth flow pump;

300-a first storage mechanism; 301-a first flow pump; 302-a second flow pump; 303-a first supplementary tube;

400-a second storage mechanism; 401-third flow pump; 402-a fourth flow pump; 403-a second supplementary tube; 404-a circulation pipe; 405-a circulation mechanism.

Detailed Description

The invention will be further explained with reference to the drawings.

The invention provides a cold and hot ablation system, a control method of the cold and hot ablation system, a control method of ice hockey size and a storage medium. The cold and hot ablation system controls the working medium flow at different stages of the operation of the system and different positions in the system, thereby realizing the technical requirements of less working medium consumption flow and larger obtained ice hockey size, for example, obtaining the double effects of least working medium consumption flow and largest obtained ice hockey size, thereby obtaining better treatment time and treatment effect and consuming less treatment working medium.

In addition, the goal of forming the ice ball with the preset size can be achieved by controlling the flow of the working medium, so that the size of the ice ball can be in a controllable range to adapt to different treatment requirements.

Therefore, the invention is different from the means of controlling the temperature and/or pressure of the working medium in the prior art, and can more directly control the flow of the working medium at different positions so as to more accurately control the size of the ice ball.

It will be appreciated by those skilled in the art that the "puck" of the present invention is a spherical puck formed in an ablation device, such as that disclosed in chinese patent CN113576648B, an ablation device, the entire text of which is incorporated herein by reference, all inconsistencies being deemed to prevail here.

The control method of the cold and hot ablation system can be used in the experiment or test stage of the cold and hot ablation system. Specifically, the control method of the present invention includes the following operation steps.

First, a pre-cooling stage.

When the system initially operates, each pipeline is precooled when the working medium flows in the system, namely a precooling stage, wherein the precooling stage is a stage for forming ice balls. At this stage, the first output side of the cooling source to be controlled outputs the working medium at the first flow rate, and the first output side of the ablation apparatus outputs the working medium at the second flow rate for precooling.

By controlling the flow of the working medium output by the cold source and the flow of the working medium output by the ablation instrument, the temperature of the pipeline and the environment can be quickly reduced to a proper temperature range, so that the ice hockey with expected larger size can be obtained.

In some embodiments, the flow rate is controlled by controlling the opening of the respective valves. Specifically, a first output side of the cooling source is controlled to output working medium at a first flow rate by adjusting the opening degree of one or more of the first valve, the phase separation valve and the second valve, and the first output side of the ablation instrument outputs working medium at a second flow rate greater than the first flow rate. Wherein the first valve is positioned at the total output side of the cold source; the phase separation valve is positioned at the first output side of the cold source; the second valve is located on a first output side of the ablation instrument.

For example, in a preferred embodiment, in the pre-cooling stage, the opening degrees of the first valve, the phase separation valve and the second valve are adjusted to be within a proper range, so that the first flow rate is maintained between 37L/min and 62/min, the second flow rate is maintained between 123L/min and 148L/min, and the consumption flow rate of the working medium is maintained between 197L/min and 227L/min.

In a more preferable embodiment, in the pre-cooling stage, the opening degree of the first valve is adjusted to be within a proper range, the opening degrees of the phase separation valve and the second valve are both adjusted to be 100%, the first flow rate can be maintained between 53L/min and 56/min, the second flow rate can be maintained between 128L/min and 131L/min, and the consumption flow rate of the working medium can be maintained between 200L/min and 207L/min. In the preferred embodiment, the opening of both the phase separation valve and the second valve are adjusted to 100%, which also acts to speed up the cooling circuit and quickly vent the pressure on the first output side of the ablation device.

In a preferred embodiment, the pre-cooling period lasts only 1-5 minutes, and the temperature of the tubing and surrounding ablation instrument has been reduced to a suitable temperature range.

In addition, an ice ball can be formed initially in the pre-cooling stage, and the size of the formed ice ball is generally less than 6mm (the minor axis diameter of the ice ball). It should be noted that, since the formed ice hockey may not be a perfect sphere, such as an ellipsoid, the "diameter" of the ice hockey or the "size" of the ice hockey refers to the minor axis diameter of the ice hockey.

The above-mentioned working medium consumption flow rate may be a flow rate of the working medium obtained from the total output side of the cold source.

Second, the ice ball growth stage.

After the pre-cooling is completed, the temperature of the pipeline and the surrounding of the ablation instrument is reduced to be within the proper temperature range. At this stage, the ice hockey begins to grow rapidly, i.e., the ice hockey growing stage. At this stage, the first output side of the cooling source to be controlled outputs working medium at a third flow rate, and the second output side of the ablation instrument outputs working medium at a fourth flow rate greater than the third flow rate, so that ice balls with preset sizes are formed in the ablation instrument. Wherein the third flow rate is also less than the first flow rate, and the fourth flow rate is greater than the second flow rate.

Likewise, the flow rate can be controlled by controlling the opening of the corresponding valve at this stage. Specifically, the first output side of the cooling source is controlled to output working medium at a third flow rate by adjusting the opening degree of one or more of the first valve, the phase separation valve, the second valve, the third valve and the fourth valve, and the second output side of the ablation instrument outputs working medium at a fourth flow rate. Wherein the third valve is located on a second output side of the ablation instrument; the fourth valve is located on a first supplemental tube connected to the second output side of the ablation device.

For example, in a preferred embodiment, in the ice ball growing stage, the first valve, the phase separation valve, the second valve and the fourth valve are adjusted to be in a proper range, so that the third flow rate is maintained between 13L/min and 27L/min, the fourth flow rate is maintained between 203L/min and 234L/min, and the consumption flow rate of the working medium is between 237L/min and 270L/min. Wherein the ice ball growth stage lasts for 8-20min, and ice balls with diameter of 18-30mm are obtained, which meet the requirement of expected size (diameter).

In a more preferable embodiment, in the ice ball growing stage, the opening degree of the first valve is adjusted to 100%, the opening degree of the phase separation valve is adjusted to 14% -18%, the opening degree of the second valve is adjusted to 8% -16%, the opening degree of the third valve is adjusted to 78% -81%, and the opening degree of the fourth valve is adjusted to 90% -93%, so that the third flow rate is maintained between 14L/min and 17L/min, the fourth flow rate is maintained between 204L/min and 211L/min, and the working medium consumption flow rate is maintained between 241L/min and 247L/min. In a preferred embodiment, the ice ball growth phase lasts 10-15min, resulting in an ice ball with a minor axis diameter of 20 mm.

At this time, since the second valve is slightly opened, the flow rate of the working medium passing through the second valve (hereinafter referred to as a seventh flow rate) can be maintained between 14L/min and 17L/min.

In the ice ball growing stage, the ice ball grows at a higher speed, so that the opening degrees of the phase separation valve and the second valve are both smaller than 100%, and the aim of saving working media can be fulfilled.

It should be noted that the duration of the ice ball growing phase is only exemplary, and for different diameters of ablation instruments, the duration of the ice ball growing phase is different, and the duration of the ice ball growing phase increases as the diameter of the ablation instrument decreases.

The first flow rate, the second flow rate, the third flow rate, and the fourth flow rate are a range, i.e., a set of flow rates. Thus, the third flow being less than the first flow may be that a maximum of the set of third flows is less than a minimum of the set of first flows; likewise, the fourth flow rate being greater than the second flow rate may be such that a minimum value in the set of fourth flow rates is greater than a maximum value in the set of second flow rates.

However, it is also conceivable for the set of third flows to intersect the set of first flows over a range and for the set of fourth flows to intersect the set of second flows over a range. In this case, it is sufficient to ensure that the traffic selected from the set of third traffic is smaller than the traffic selected from the set of first traffic, and the traffic selected from the set of fourth traffic is larger than the traffic selected from the set of second traffic. In other words, only the specific selected third flow rate is less than the selected first flow rate, and only the specific selected fourth flow rate is greater than the selected second flow rate.

And thirdly, a puck stabilization phase.

After the desired puck is obtained, it needs to be maintained at the desired size, i.e., puck stabilization phase. At this stage, a certain amount of working medium needs to be output to the ablation device to prevent the ice hockey from being reduced in size in the process of heat exchange (namely, the cold output by the ablation device is smaller than the heat dissipation amount between the ice hockey and the outside of the ice hockey). Specifically, the first input side of the ablation instrument can be controlled to input the treatment working medium at a fifth flow rate, and the third output side of the ablation instrument can output the treated working medium at a sixth flow rate, so that the size of the ice ball formed in the ablation instrument is maintained within a preset size range. Wherein the sixth flow rate is less than the fourth flow rate.

Likewise, the flow rate can be controlled by controlling the opening of the corresponding valve at this stage. Specifically, the opening degree of the phase separation valve, the second valve and the third valve is zero, and one or more of the first valve, the fifth valve and the sixth valve is/are regulated to control the first input side of the ablation apparatus to input the treatment working medium at a fifth flow rate, and the third output side of the ablation apparatus to output the treated working medium at a sixth flow rate. Wherein the fifth valve is located on a second supplemental tube connected to the first input side of the ablation instrument; the sixth valve is located on a third output side of the ablation instrument.

For example, in a preferred embodiment, in the ice hockey stabilization stage, the opening degrees of the first valve, the fifth valve and the sixth valve are adjusted to be within a proper range, the opening degree of the phase separation valve is adjusted to be 0, the opening degree of the second valve is adjusted to be 0, and the opening degree of the third valve is adjusted to be 0, so that the fifth flow rate is maintained between 34L/min and 56L/min, the sixth flow rate is maintained between 141L/min and 185L/min, and the working medium consumption flow rate is maintained between 142L/min and 155L/min.

In a more preferred embodiment, in the ice hockey stabilization stage, the opening degree of the first valve is adjusted to 83-85%, the opening degree of the phase separation valve is adjusted to 0, the opening degree of the second valve is adjusted to 0, the opening degree of the third valve is adjusted to 0, the opening degree of the fourth valve is adjusted to 0, the opening degree of the fifth valve is adjusted to 66-69%, and the opening degree of the sixth valve is adjusted to 90-95%, so that the fifth flow rate is maintained between 37L/min and 43L/min, the sixth flow rate is maintained between 162L/min and 168L/min, and the working medium consumption flow rate is 146L/min and 150L/min. In this embodiment, the puck stabilization phase duration is less than 6 min.

In addition, the size of the ice hockey may also increase from the ice hockey growth stage to the ice hockey stabilization stage.

In this example, the puck stabilization phase ends for the end of the system shutdown.

In order to measure the flow and consider the recycling of the working medium, thereby reducing the consumption of the working medium, the flow meter is realized by additionally arranging a first storage mechanism, a second storage mechanism and a corresponding flow pump.

Specifically, working medium output by the first output side of the cold source and working medium output by the first output side of the ablation instrument are respectively collected through the first storage mechanism. Therefore, the first flow and the third flow are respectively the flow of the working medium which is output to the first storage mechanism from the first output side of the cold source through the first flow pump; the second flow is the flow of the working medium which is output to the first storage mechanism from the first output side of the ablation instrument through the second flow pump.

In addition, the first storage mechanism is connected with the first supplement pipe to provide working medium to the second output side of the ablation device through the first supplement pipe. In the growth stage of the ice hockey, the pressure of the output side (second output side) of the ablation instrument is increased under the action of the first supplement pipe, so that the heat exchange time of the working medium in the ablation instrument can be prolonged, and the ice hockey can grow rapidly.

Working medium output from the second output side of the ablation instrument is collected through the second storage mechanism. Therefore, the fourth flow is the flow of the working medium which is output to the second storage mechanism from the second output side of the ablation instrument through the third flow pump.

The second storage mechanism is also connected with a second supplementing pipe so as to provide working medium to the first input side of the ablation instrument through the second supplementing pipe. In the ice hockey stabilizing stage, the cold output by the melting instrument can be kept not less than the heat dissipation capacity of the ice hockey and the outside of the ice hockey through the action of the second supplementing pipe so as to stabilize the size of the ice hockey.

The second storage mechanism is also connected with the cold source so as to recycle the working medium in the second storage mechanism to the cold source.

The total amount of the working medium output from the total output of the heat sink 100 can be obtained by the heat sink flow pump 101 shown in fig. 1, which is disposed on the total output of the heat sink 100.

Therefore, the control of each valve mechanism ensures that the first flow rate is maintained between 37L/min and 62L/min (preferably 53L/min and 56L/min), the second flow rate is maintained between 123L/min and 148L/min (preferably 128L/min and 131L/min) in the pre-cooling stage, and the consumption flow rate of the working medium in the pre-cooling stage is between 197L/min and 227L/min (preferably 200L/min and 207L/min).

In the ice ball growing stage, the third flow rate is maintained to be 13L/min-27L/min (preferably 18L/min-22L/min), the fourth flow rate is maintained to be 203L/min-234L/min (preferably 204L/min-211L/min), and the working medium consumption flow rate in the pre-cooling stage is 237L/min-270L/min (preferably 241L/min-247L/min).

In the ice hockey stabilizing stage, the fifth flow is maintained to be between 34L/min and 56L/min (preferably between 37L/min and 43L/min), the sixth flow is maintained to be between 141L/min and 185L/min (preferably between 162L/min and 168L/min), and the working medium consumption flow in the ice hockey stabilizing stage is between 142L/min and 155L/min (preferably between 146L/min and 150L/min).

By precise control of the above-mentioned respective flow rates, ice balls having a minor axis diameter of 25mm to 30mm can be obtained, which may be sufficient to meet the intended requirements.

According to a second aspect of the present invention, there is provided a method for controlling puck size for use in an experimental or testing phase of a thermal ablation system. The ice hockey size control method comprises the following steps:

the first stage is as follows: and adjusting the opening degree of the valve mechanism to enable the first output side of the cold source to output the working medium at a first flow rate, and the first output side of the ablation instrument to output the working medium at a second flow rate to pre-cool, wherein the second flow rate is greater than the first flow rate.

The first stage may be a pre-cooling stage as described herein.

Further, the valve mechanism includes:

a first valve 1 disposed at a general output side of the cool source 100;

a phase separation valve 11 disposed at a first output side of the cool source; and

the second valve 2 is arranged on the first output side of the ablation instrument, and the second flow can be the flow of working medium flowing through the second valve 2;

wherein, by controlling the opening degree of one or more of the first valve 1, the phase separation valve 11 and the second valve 2, the first output side of the cold source 100 can output the working medium at the third flow rate, and the second output side of the ablation apparatus 200 can output the working medium at the fourth flow rate.

The first flow rate may be the flow rate of the working medium flowing through the phase separation valve 11 in the first stage; the second flow rate may be the flow rate of the working medium flowing through the second valve 2 in the first stage. The flow rate of the working medium flowing through the first valve 1 in the first stage is the working medium consumption flow rate in the first stage.

The first valve 1, the phase separation valve 11 and the second valve 2 are each linear flow valves in character, i.e. the relative flow through the valve is approximately linear with the relative opening of the valve, in other words the change in flow caused by its one-stroke change is approximately constant.

The flow rate of the working medium flowing through the corresponding valve in the valve mechanism and the opening degree of the valve satisfy the following relational expression (10):

wherein the content of the first and second substances,Qthe flow rate of the working medium which flows through the corresponding valve at present;

Rthe ratio between the maximum flow and the minimum flow that can be controlled by the respective valve,Rthe following expression is satisfied:R=Q _max /Q _min ；

Q _max the theoretical maximum flow value of the working medium can be passed through for the corresponding valve;

Q _min the theoretical minimum flow value of the working medium can be passed through for the corresponding valve;

Lis the current opening of the corresponding valve;

L _max is the theoretical maximum value of the opening degree of the corresponding valve.

Generally, the theory of the valve is the bestLow flow rate valueQ _min Is the theoretical maximum flow value of the valveQ _max 2% -3% of (i.e.RIs 33-50.

For example, the flow rate of the working medium flowing through the first valve 1 and the opening degree of the first valve 1 satisfy the following relation (1):

wherein the content of the first and second substances,Q ₁ the flow rate of the working medium which currently flows through the first valve 1;

R ₁ is the ratio between the maximum flow and the minimum flow that the first valve 1 can control,R ₁ the following expression is satisfied:R ₁ =Q _1max / Q _1min ；

Q _1max the theoretical maximum flow value of the working medium which can pass through the first valve 1 is obtained;

Q _1min the theoretical minimum flow value of the working medium can be passed through by the first valve 1;

L ₁ is the current opening of the first valve 1;

L _1max is the theoretical maximum value of the opening degree of the first valve 1.

Therefore, when the opening degree of the first valve 1 is 50%, that is, the above-describedL ₁ /L _1max =50%, the ratio of the flow rate of the working medium passing through the first valve 1 to the theoretical maximum flow rate of the working medium that can pass through the first valve 1 can be calculated according to the above formula (1) at this time asQ ₁ /Q _1max =51.7%。

Similarly, the flow rate of the working medium flowing through the phase separation valve 11 and the opening degree of the phase separation valve 11 satisfy the following relational expression (11):

wherein the content of the first and second substances,Q ₁₁ the flow rate of the working medium which currently flows through the phase separation valve 11;

R ₁₁ the ratio of the maximum flow rate and the minimum flow rate that can be controlled by the phase separation valve 11,R ₁₁ the following expression is satisfied:R ₁₁ = Q _11max /Q _11min ；

Q _11max the phase separation valve 11 can pass the theoretical maximum flow value of the working medium;

Q _11min the phase separation valve 11 can pass the theoretical minimum flow value of the working medium;

L ₁₁ is the current opening degree of the phase separation valve 11;

L _11max which is the theoretical maximum opening of the phase separation valve 11.

Similarly, the flow rate of the working medium flowing through the second valve 2 and the opening degree of the second valve 2 satisfy the following relation (2):

wherein the content of the first and second substances,Q ₂ the flow rate of the working medium which currently flows through the second valve 2;

R ₂ is the ratio between the maximum flow and the minimum flow that the second valve 2 can control,R ₂ the following expression is satisfied:R ₂ =Q _2max / Q _2min ；

Q _2max the theoretical maximum flow value of the working medium which can pass through the second valve 2;

Q _2min the theoretical minimum flow value of the working medium which can pass through the second valve 2;

L ₂ is the current opening of the second valve 2;

L _2max is the theoretical maximum value of the opening degree of the second valve 2.

And a second stage: adjusting the opening degree of the valve mechanism to enable the first output side of the cold source to output working media at a third flow rate, and the second output side of the ablation instrument to output working media at a fourth flow rate to enable ice balls with preset sizes to be formed in the ablation instrument, wherein the fourth flow rate is larger than the third flow rate; the second stage may be a pre-cooling stage as described above.

By adjusting the opening and flow of the valves, ice balls with the size of 1-6mm can be obtained in the first stage. It will be appreciated that the above dimensions are the minor axis diameter of the puck.

The ice hockey size control method further comprises the following steps:

and a second stage: and adjusting the opening degree of the valve mechanism to enable the first output side of the cold source to output working media at a third flow rate, and the second output side of the ablation instrument to output working media at a fourth flow rate to enable ice balls with preset sizes to be formed in the ablation instrument, wherein the fourth flow rate is greater than the third flow rate.

The second stage may be the ice hockey growing stage described above.

The valve mechanism further includes:

a third valve 3 disposed on a second output side of the ablation instrument 200; and

a fourth valve 4 provided on the first supplementary tube 303 connected to the second output side of the ablation instrument 200;

wherein, by controlling the opening degree of one or more of the first valve 1, the phase separation valve 11, the second valve 2, the third valve 3 and the fourth valve 4, the first output side of the cold source 100 can output the working medium at the third flow rate, and the second output side of the ablation apparatus 200 can output the working medium at the fourth flow rate. The third flow rate can be the flow rate of the working medium flowing through the phase separation valve 11 in the second stage; the fourth flow rate may be the flow rate of the working medium flowing through the third valve 3 in the second stage. The flow rate of the working medium flowing through the first valve 1 in the second stage is the working medium consumption flow rate in the second stage.

The flow rate of the working medium flowing through the first valve 1 and the opening degree of the first valve 1, the flow rate of the working medium flowing through the second valve 2 and the opening degree of the second valve 2, and the flow rate of the working medium flowing through the phase separation valve 11 and the opening degree of the phase separation valve 11 may satisfy the above-described relational expression (10) or the above-described relational expressions (1), (11), and (2).

The flow rate of the working medium flowing through the third valve 3 and the opening degree of the third valve 3 satisfy the following relational expression (3):

wherein the content of the first and second substances,Q ₃ the flow rate of the working medium which flows through the third valve 3 at present;

R ₃ the ratio between the maximum flow and the minimum flow that can be controlled by the third valve 3,R ₃ the following expression is satisfied:R ₃ =Q _3max / Q _3min ；

Q _3max the third valve 3 can pass the theoretical maximum flow value of the working medium;

Q _3min the third valve 3 can pass the theoretical minimum flow value of the working medium;

L ₃ the current opening degree of the third valve 3;

L _3max the theoretical maximum opening degree of the third valve 3.

By adjusting the opening and flow of the valves, ice balls with the size of 18-30mm can be obtained in the second stage. It will be appreciated that the above dimensions are the minor axis diameter of the puck.

Further, the seventh flow rate may be the flow rate of the working medium through the second valve 2 in the second stage. In the second phase, the flow rate of the working medium flowing through the second valve 2 and the opening degree of the second valve 2 still satisfy the above-mentioned relation (2).

It will be appreciated that the flow rate of the working medium through the fourth valve 4 and the opening degree of the fourth valve 4 satisfy the following relation (4):

wherein the content of the first and second substances,Q ₄ the flow rate of the working medium which currently flows through the fourth valve 4;

R ₄ is the ratio between the maximum flow and the minimum flow that the fourth valve 4 can control,R ₄ the following expression is satisfied:R ₄ =Q _4max / Q _4min ；

Q _4max the theoretical maximum flow value of the working medium can be passed through by the fourth valve 4;

Q _4min the theoretical minimum flow value of the working medium can be passed through by the fourth valve 4;

L ₄ is the current opening degree of the fourth valve 4;

L _4max is the theoretical maximum value of the opening degree of the fourth valve 4.

The valve mechanism further includes:

a fifth valve 5 arranged on a second supplementary tube 403 connected to the first input side of the ablation instrument 200; and

a sixth valve 6 disposed on a third output side of the ablation instrument 200.

The method for controlling the ice hockey size further comprises the following steps:

and a third stage: by adjusting the opening degree of one or more of the first valve 1, the fifth valve 5 and the sixth valve 6, the first input side of the ablation apparatus 200 inputs the treatment working medium at a fifth flow rate, and the third output side of the ablation apparatus 200 outputs the treated working medium at a sixth flow rate, wherein the sixth flow rate is greater than the fifth flow rate.

The third stage is the puck stabilization stage described herein.

The fifth flow rate can be the flow rate of the working medium flowing through the fifth valve 5 in the third stage; the sixth flow rate may be the flow rate of the working medium flowing through the sixth valve 6 at the third stage. The flow rate of the working medium flowing through the first valve 1 in the third stage is the working medium consumption flow rate in the third stage.

The flow rate of the working medium flowing through the first valve 1 and the opening degree of the first valve 1 may satisfy the above-mentioned relation (10) or the above-mentioned relation (1).

The flow rate of the working medium flowing through the fifth valve 5 and the opening degree of the fifth valve 5 satisfy the following relational expression (5):

wherein the content of the first and second substances,Q ₅ the flow rate of the working medium which currently flows through the fifth valve 5;

R ₅ is the ratio between the maximum flow and the minimum flow that the fifth valve 5 can control,R ₅ the following expression is satisfied:R ₅ =Q _5max / Q _5min ；

Q _5max the theoretical maximum flow value of the working medium which can pass through the fifth valve 5;

Q _5min the theoretical minimum flow value of the working medium can be passed through by the fifth valve 5;

L ₅ is the current opening degree of the fifth valve 5;

L _5max is the theoretical maximum value of the opening degree of the fifth valve 5.

The flow rate of the working medium flowing through the sixth valve 6 and the opening degree of the sixth valve 6 satisfy the following relational expression (6):

wherein the content of the first and second substances,Q ₆ the flow rate of the working medium which currently flows through the sixth valve 6;

R ₆ is the ratio between the maximum flow and the minimum flow that the sixth valve 6 can control,R ₆ the following expression is satisfied:R ₆ =Q _6max / Q _6min ；

Q _6max the theoretical maximum flow value of the working medium can be passed through by the sixth valve 6;

Q _6min the theoretical minimum flow value of the working medium can be passed through by the sixth valve 6;

L ₆ is the current opening degree of the sixth valve 6;

L _6max the theoretical maximum value of the opening degree of the sixth valve 6.

The size of the ice hockey ball can be kept within the range of 25-35mm in the third stage by adjusting the opening and flow rate of each valve. It will be appreciated that the above dimensions are the minor axis diameter of the puck.

The flow rate of the working fluid through each valve may correspond (be the same or similar) to the flow rate of the fluid obtained by the corresponding flow pump mechanism, irrespective of losses.

For example, in the first phase, the second flow rate is the flow rate of the working medium flowing through the second valve 2, which satisfies the above-mentioned relation (10) or relation (2) with the opening degree of the second valve 2. The second flow rate may also be obtained by a second flow pump 302 described below. In the second stage, the fourth flow rate is the flow rate of the working medium flowing through the third valve 3, and the fourth flow rate and the opening degree of the third valve 3 satisfy the above-mentioned relation (10) or relation (3).

In the first stage, the opening degree of the second valve 2 is 100%, and according to the relation (2), the second flow rate is 130L/min; which is approximately the same flow rate as that obtained by the second flow pump 302 described below. In the second stage, the opening degree of the third valve 3 is 80%, and according to the relation (3), the fourth flow rate of 205L/min, which is substantially the same as the flow rate obtained by the third flow pump 401 described later (see example 1), can be obtained. In the method for controlling the ice hockey size, the ice hockey size refers to the minor axis diameter of the ice hockey.

It should be understood that the control method of the cryoablation system and the control method of the ice hockey size of the present invention may be based on the cryoablation system described below, and thus the specific forms of the components involved in the control method of the cryoablation system and the control method of the ice hockey size of the present invention are not described in detail. The control method of the thermal ablation system and the control method of the ice hockey size of the present invention can be combined with the various components and their connection modes of the thermal ablation system described in any one or more of the above or below embodiments/examples without any obstacles.

According to a third aspect of the present invention, there is provided a storage medium having stored thereon a computer program which, when being executed by a processor, carries out the steps of the method for controlling a thermal ablation system as described above or the steps of the method for controlling a puck size as described above. According to a fourth aspect of the present invention, a thermal ablation system is provided.

As shown in fig. 1, the thermal ablation system of the present invention can be used to implement the control method of the thermal ablation system and the control method of the ice hockey size. Specifically, the thermal ablation system of the present invention includes a cold source 100, an ablation instrument 200, a first storage mechanism 300, a second storage mechanism 400, a valve mechanism, and a flow pump mechanism. The cold source 100 may be a cold tank for storing and supplying a working medium, such as liquid nitrogen. The ablation instrument 200 may be an ablation needle, an ablation pen, an ablation chamber, etc., which is used for performing cold-hot ablation therapy using a working fluid (cold working fluid or hot working fluid). The first storage means 300 and the second storage means 400 may be configured as a cold tank, or may be configured as a normal-temperature and normal-pressure storage tank.

The valve mechanism may be a first valve 1, a second valve 2, a third valve 3, a fourth valve 4, a fifth valve 5, and a sixth valve 6, described below. The valve mechanism is adjustable in opening degree, and may be, for example, a solenoid valve. The above-mentioned valves are characterized by a linear flow rate characteristic, that is, the relative flow rate passing through the valve and the relative opening degree of the valve are approximately in a linear relationship, in other words, the flow rate change due to the one-stroke change thereof is approximately constant. The flow pump mechanisms may be a first flow pump 301, a second flow pump 302, a third flow pump 401, a fourth flow pump 402, a fifth flow pump 231, and a cold source flow pump 101, described below. The flow pump mechanism is used to monitor and measure the flow of fluid therethrough, and may be, for example, an existing flow pump suitable for working fluids such as liquid nitrogen.

As shown in fig. 1, the total output side of the cool source 100 is provided with a first valve 1 and a cool source flow pump 101. The cold source flow pump 101 can obtain the amount of the working medium (i.e., the working medium consumption flow) output by the cold source 100 at each stage and the total amount of the working medium (i.e., the total working medium consumption flow). Downstream of the first valve 1, the total output side of the cold source 100 is divided into two branches, namely a first cold source output pipe 110 (i.e. corresponding to the first output side of the cold source 100) and a second cold source output pipe 120 (i.e. corresponding to the second output side of the cold source 100). The first cold source output pipe 110 is provided with a phase separation valve 11, and the first cold source output pipe 110 is connected with the first storage mechanism 300; the second cold source output tube 120 is connected to the first input side of the ablation instrument 200.

Therefore, the cold source 100 is divided into two paths by the working medium output by the cold source flow pump 101, one path reaches the first storage mechanism 300 through the first cold source output pipe 110 by the action of the first flow pump 301, and the other path reaches the first input side of the ablation apparatus 200 through the second cold source output pipe 120.

Therefore, the heat source flow pump 101 can obtain the consumption flow of the working medium in each stage (or the sum of the consumption flows of the working medium in the three stages). The first flow pump 301 can obtain the first flow rate of the pre-cooling stage and the third flow rate of the ice ball growing stage respectively. In order to ensure the accuracy of the measured flow, the cold source flow pump 101 is disposed downstream of the first valve 1, and the first flow pump 301 is disposed downstream of the phase separation valve 11.

As shown in fig. 1, the output side of the ablation device 200 is provided with a first ablation device output tube 210, a second ablation device output tube 220 and a third ablation device output tube 230, respectively.

The first output pipe 210 of the ablation apparatus is connected to the first storage mechanism 300, and the second valve 2 and the second flow pump 302 are connected thereto, i.e. the working medium output by the ablation apparatus 200 can be recovered and stored by the first storage mechanism 300. A second flow rate during the pre-cooling phase and a seventh flow rate during the ice ball growing phase (measured when the second valve 2 is opened) are respectively obtained by the second flow pump 302. The second flow pump 302 is arranged downstream of the second valve 2 to ensure accuracy of the measured flow.

The second output tube 220 of the ablation apparatus is connected to the second storage mechanism 400, and is connected to the third valve 3 and the third flow pump 401, i.e. the working medium output by the ablation apparatus 200 can be recovered and stored by the second storage mechanism 400. A fourth flow rate for the ice ball growth stage may be obtained by the third flow pump 401. A third flow pump 401 is arranged downstream of the third valve 3 to ensure accuracy of the measured flow.

In addition, the second ablation instrument output tube 220 is also connected with a first supplementary tube 303, and the first supplementary tube 303 extends into the first storage mechanism 300, so that working medium can be conveyed to the second ablation instrument output tube 220 through the first supplementary tube 303 to increase the pressure on the output side of the ablation instrument 200.

The third output pipe 230 of the ablation apparatus is connected with a sixth valve 6 and a fifth flow pump 231, i.e. the working medium output by the ablation apparatus 200 can be discharged to the environment. The second reservoir mechanism 400 is connected to a second input side of the ablation instrument 200 via a second supplemental tube 403, and the fifth valve 5 and a fourth flow pump 402 are connected to the second supplemental tube 403.

The fifth flow rate for the ice hockey puck stabilization stage is available through the fourth flow pump 402 and the sixth flow rate for the ice hockey puck stabilization stage is available through the fifth flow pump 231. Wherein the fourth flow pump 402 is located downstream of the fifth valve 5 and the fifth flow pump 231 is located downstream of the sixth valve 6 to ensure accuracy of the measured flow.

During the puck stabilization phase, working fluid may be input to the input side of the ablation device 200 via the second storage mechanism 400 to prevent the puck size from decreasing during heat exchange with the outside world.

The second storage mechanism 400 is connected to the cold source 100 through a circulation pipe 404, and a circulation mechanism 405 is connected to the circulation pipe 404, and the circulation mechanism 405 may be a pump or an air compressor. After the ice ball stabilization phase is completed, if there is a large amount of liquid nitrogen in the second storage mechanism 400, the liquid nitrogen can be pumped back to the cold source 100 through the pump, and if there is no large amount of liquid nitrogen in the second storage mechanism 400, the air compressor needs to be turned on, and the nitrogen is pumped back to the cold source 100.

The control method of the present invention will be described in detail by taking the thermal ablation system shown in fig. 1 as an example.

First, in a pre-cooling phase.

At this stage, it is necessary to ensure that the pressure within the cold source 100 is maintained within a certain interval. At normal pressure, the liquid nitrogen temperature was-196 ℃. In order to maintain the liquid nitrogen at the operating temperature, the pressure within cold source 100 needs to be guaranteed.

At this stage, the opening degree of the first valve 1 is adjusted to 68% to 73%, and the opening degrees of the phase separation valve 11 and the second valve 2 are both adjusted to 100%, in order to shorten the time for cooling the pipeline. Wherein, the first output side of the ablation apparatus 200 can be rapidly decompressed to promote cooling of the pipeline because the opening degree of the second valve 2 is 100%. The working medium output from the first output side of the cold source 100 or the working medium output from the first output side of the ablation apparatus 200 is recovered and reused by the first storage mechanism 300, so that the consumption of the working medium can be reduced.

Preferably, in the pre-cooling stage, when the opening degree of the first valve 1 is 68% -73%, and the opening degrees of the phase separation valve 11 and the second valve 2 are 100%, the first flow rate obtained from the first flow pump 301 is 53-56L/min, and the second flow rate obtained from the second flow pump 302 is 128-131L/min. The working medium consumption flow obtained from the cold source flow pump 101 at the stage is 200-207L/min. In addition, another important role of the first storage mechanism 300 is that it is connected to the first flow pump 301 for obtaining the first flow rate and the third flow rate and the second flow pump 302 for obtaining the second flow rate, respectively, and heat exchange occurs while the working medium cools the pipeline, so that the working medium is changed into gas (nitrogen), and thus the working medium collected by the first storage mechanism 300 may be nitrogen at normal temperature and normal pressure (or there may also be liquid nitrogen that is not completely changed into nitrogen in part), and thus the flow rate of the gas may be monitored and measured more conveniently and accurately by the first flow pump 301 and the second flow pump 302 (compared to cryogenic liquid, the flow rate monitoring of the gas may be more convenient and accurate).

Preferably, in the pre-cooling phase, for the same diameter of the ablation instrument 200, the difference between the second flow rate corresponding to the second flow pump 302 and the first flow rate corresponding to the first flow pump 301 is larger, so that the duration of the pre-cooling phase is shorter.

Furthermore, the duration of the pre-cooling phase may vary for different diameters of the ablation device 200. In general. The smaller the diameter of the ablation instrument 200, the longer the duration of the pre-cooling phase. Because the smaller the diameter of the ablation instrument 200, the greater its internal resistance, the less likely the cold will exchange heat inside the conduit, and thus a correspondingly longer pre-cooling time will be required.

Preferably, in the pre-cooling stage, the opening degree of the phase separation valve 11 is kept at 100%, so that the duration of the pre-cooling stage is lower, the diameter of ice balls formed in the pre-cooling stage is larger, and the consumption flow rate of the working medium is lower.

Preferably, in the pre-cooling stage, the opening degree of the first valve 1 can be kept below 80% instead of 100%, so that the consumption flow of the working medium can be reduced, and the purpose of saving the working medium is achieved.

Second, during the ice hockey growth stage.

After the pre-cooling stage, the temperature around the pipeline and the ablation needle is reduced to a proper temperature range, such as about-150 ℃. At this stage, the openings of the phase separation valve 11 and the second valve 2 need to be reduced to avoid wasting a large amount of working medium, so that the pressure on the second output side of the ablation apparatus 200 needs to be increased to prolong the heat exchange time of the working medium in the ablation apparatus 200 to promote the rapid growth of the ice hockey.

Since the working medium is collected by the first storage mechanism 300, the working medium can be provided to the second output side of the ablation apparatus 200 through the first storage mechanism 300, and at this time, the opening degree of the fourth valve 4 needs to be kept within a proper range, so that the first storage mechanism 300 provides the working medium to the second output side of the ablation apparatus 200 through the first supplement pipe 303.

In addition, when the first storage means 300 supplies the working fluid, it is necessary to maintain the internal pressure thereof within a certain range, and therefore it is also necessary to maintain the opening degree of the first valve 1 at 100% and maintain the opening degree of the phase separation valve 11 within a proper range.

At this stage, the opening degree of the third valve 3 is kept within a proper range, so that the ablation instrument 200 can output the working medium to the second storage mechanism 400 through the second output side, and in addition, the opening degree of the second valve 2 can be 0, namely the ablation instrument 200 does not output the working medium to the first storage mechanism 300 any more; or the second valve 2 may be maintained in a slightly opened state, for example, an opening degree thereof may be 8% -16%, so that it may be facilitated that liquid nitrogen that has not undergone a phase change is collected into the first storage means 300 through the second valve 2.

One of the functions of the second storage mechanism 400 is to output the recovered working medium so as to reduce the waste of the working medium, and the collected working medium can be used for subsequent circulation. In addition, another important role of the second storage mechanism 400 is that it is connected to a third flow pump 401 for obtaining a fourth flow, and the working medium in the ablation apparatus 200 is heat-exchanged and thus is changed into gas (nitrogen), so that the working medium collected by the second storage mechanism 400 can be nitrogen at normal temperature and normal pressure, which is beneficial to more convenient and accurate monitoring and measurement of the flow by the third flow pump 401 (compared with cryogenic liquid, flow monitoring of gas is more convenient and accurate).

In the ice hockey growing stage, for the ablation apparatus 200 with the same diameter, the difference between the third flow rate corresponding to the first flow pump 301 and the fourth flow rate corresponding to the third flow pump 401 is larger, so that the duration of the ice hockey growing stage can be shorter.

Preferably, in the ice ball growing stage, when the opening degree of the first valve 1 is 100%, the opening degree of the phase separation valve 11 is 14% -18%, the opening degree of the second valve 2 is 8% -16%, the opening degree of the third valve 3 is 78% -81%, and the opening degree of the fourth valve 4 is 90% -93%, it is ensured that the third flow rate obtained from the first flow pump 301 is 18-22L/min, and the fourth flow rate obtained from the third flow pump 401 is 204-211L/min. The working medium consumption flow obtained from the cold source flow pump 101 at the stage is 241-247L/min.

In the ice ball growing stage, the second valve 2 is slightly opened, so that the flow rate (i.e. the seventh flow rate) of the working medium passing through the second valve 2 is 14-17L/min.

Furthermore, by adjusting the first flow rate, the second flow rate, the third flow rate and the fourth flow rate, the ice hockey size can be adjusted and the working medium consumption flow rate can be controlled, so that the ice hockey ablation device is suitable for different ablation instruments 200 and different treatment strategies.

In addition, the duration of the ice hockey growth phase varies for different diameters of the ablation device 200. In general. The larger the diameter of the ablation instrument 200, the longer the duration of the puck growth phase.

Third, during the puck stabilization phase.

After the puck growth stage, a puck of the desired size (diameter), for example, a puck having a minor axis of 25mm in diameter, has been obtained. It is therefore desirable to keep the size of the puck at this desired size without decreasing while the treatment is continued.

Based on the fact that a part of the working fluid has been recovered by the second storage means 400 in the previous stage, the working fluid therein can be supplied to the second input end of the ablation instrument 200 through the second supplement pipe 403 to maintain a certain cold input, thereby adjusting the opening degree of the fifth valve 5 to a proper range.

At this stage, the opening degree of the phase separation valve 11, the second valve 2, the third valve 3 and the fourth valve 4 may be adjusted to 0 (i.e., closed), so that the pressure in the second storage mechanism 400 may be maintained within a certain range to facilitate the replenishment of the working medium to the ablation device 200.

Meanwhile, the opening degree of the first valve 1 does not need to be set to 100%, a part of working medium is provided for the ablation instrument 200 through the cold source 100, the working medium is supplemented for the ablation instrument 200 through the second storage mechanism 400, and the cold quantity can be kept in a proper range so as to maintain the size of the ice hockey.

In this stage, the opening degree of the first valve 1 is 83-85%, the opening degree of the fifth valve 5 is 66-69%, and the opening degree of the sixth valve 6 is 90-95%, so that the fifth flow rate is 37-43L/min, and the sixth flow rate is 162-168L/min. The consumption flow of the working medium (obtained from the cold source flow pump 101) at this stage is 146-150L/min.

At this stage, the working medium output from the third output side of the ablation apparatus 200 can be directly discharged to the environment, which has no collection value, so that the opening degree of the sixth valve 6 can be kept in a proper range, and the working medium output from the third output side of the ablation apparatus 200 can be output according to a sixth flow rate.

The puck stabilization phase continues until the end of the system shutdown.

After completion, the first and

second storage mechanisms

300 and 400 may still contain working fluid, which can be discharged for the next operation of the system. For example, the opening degrees of the second valve 2 and the fourth valve 4 may be adjusted to 100%, and the circulation mechanism 405 is activated, and the working fluid in the first storage mechanism 300 and the second storage mechanism 400 may be discharged to the heat sink 100.

The circulating mechanism 405 may be a pump and an air compressor, wherein if more liquid nitrogen working medium is left in the second storage mechanism 400, the pump may be started so as to pump the working medium therein into the cold source 100 through the circulating pipe 404; if the second storage mechanism 400 contains less working fluid, the air compressor can be started to pump the nitrogen back to the cold source 100 through the circulation pipe 404.

The method and system of the present invention are illustrated below by specific examples and comparative examples.

Example 1

A thermal ablation system as shown in fig. 1 is used, wherein the ablation instrument 200 is an ablation needle. The diameter of the ablation needle is 2 mm.

In the pre-cooling stage, the opening degree of the first valve 1 is controlled to be 68-73%, and the opening degrees of the phase separation valve 11 and the second valve 2 are both controlled to be 100%. Therefore, the working fluid in the cold source 100 can flow through the phase separation valve 11 and the first cold source output pipe 110 quickly to cool the pipeline, and the pressure of the ablation instrument 200 can be released quickly through the second valve 2.

Through the combination of the opening degrees of the first valve 1, the phase separation valve 11 and the second valve 2 in the embodiment, the working medium flow rate corresponding to the first flow pump 301 can be controlled to be the first flow rate, and the working medium flow rate corresponding to the second flow pump 302 can be controlled to be the second flow rate.

In the ice ball growing stage, the opening degree of the first valve 1 is controlled to be 100%, and the opening degrees of the phase separation valve 11 and the second valve 2 are both controlled to be 16%. The opening degree of the third valve 3 is controlled to 80%, and the opening degree of the third valve 3 is controlled to 90%.

By the combination of the opening degrees of the first valve 1, the phase separation valve 11, the second valve 2, the third valve 3 and the fourth valve 4, the working medium flow rate corresponding to the first flow pump 301 can be controlled to be the third flow rate, and the working medium flow rate corresponding to the third flow pump 401 can be controlled to be the fourth flow rate.

In the ice ball stabilization phase, the opening degree of the first valve 1 is controlled to be 83%, and the opening degrees of the phase separation valve 11, the second valve 2, the third valve 3, and the fourth valve 4 are all controlled to be 0 (i.e., closed). The opening degree of the fifth valve 5 is controlled to be 66%, and the opening degree of the sixth valve 6 is controlled to be 90%.

In the three processes, the cold source flow pump 101 can measure the corresponding working medium consumption flow, which is specifically shown in table 1 below.

By the combination of the opening degrees of the first valve 1, the fifth valve 5 and the sixth valve 6 in the embodiment, the working medium flow rate corresponding to the controllable fifth flow pump 231 can be controlled to be the sixth flow rate, and the working medium flow rate corresponding to the controllable fourth flow pump 402 can be controlled to be the fifth flow rate.

The opening degree of the valve mechanism and the flow rate data of the flow rate pump mechanism in example 1 are shown in table 1.

TABLE 1 opening degree of valve mechanism and flow data table of flow pump mechanism

In this embodiment 1, the opening degrees of the valves at different stages are adjusted to control the working medium flow rates at different output sides/input sides, so as to obtain an optimal combination scheme of the working medium consumption flow rate (i.e., the flow rate obtained by the cold source flow pump 101) and the ice ball diameter, that is, the working medium consumption flow rate is lower, and the ice ball diameter is larger.

Example 2

Embodiment 2 employs the thermal ablation system of fig. 1, wherein the ablation device 200 is an ablation needle. The diameter of the ablation needle is the same as that of the ablation needle of example 1 described above. In contrast, in embodiment 2, the opening degree of the first valve 1 in the pre-cooling stage is changed, so that both the first flow rate and the second flow rate in the pre-cooling stage are increased, and specific values are shown in table 2.

TABLE 2 opening degree of valve mechanism and flow data table of flow pump mechanism

In the pre-cooling stage of example 2, the first flow rate and the second flow rate were increased relative to the first flow rate and the second flow rate of example 1, respectively. As can be seen from table 2, the duration of the pre-cooling phase in example 2 is shorter, and the ice ball diameter obtained in the pre-cooling phase is also larger.

However, since the second flow rate in embodiment 2 is increased, the working medium flow rate corresponding to the cold source flow rate pump 101 is also increased compared to embodiment 1, that is, the working medium consumption flow rate is greater than that in embodiment 1. In other words, although the diameter of the ice ball is larger in example 2, the consumption flow rate of the working medium is increased in the precooling stage.

Example 3

Embodiment 3 the thermal ablation system of fig. 1 is used, wherein the ablation device 200 is an ablation needle. The diameter of the ablation needle is the same as that of the ablation needle of example 1 described above. In contrast, in example 3, the opening degree of the third valve 3 in the ice ball growing stage was changed, and specific numerical values are shown in table 3.

TABLE 3 opening degree of valve mechanism and flow data table of flow pump mechanism

As is clear from table 3, in example 3, the opening degree of the third valve 3 was increased in addition to that in example 1, and the opening degrees of the remaining valves were kept the same as those in example 1, so that the fourth flow rate was significantly increased. That is, during the ice ball growth phase, the flow rate at the output side of the ablation device 200 is increased compared to example 1. As can be seen from table 3, the time for the ice ball growth phase in example 3 was shorter, and the diameter of the obtained ice ball was larger than that of the ice ball in example 1.

However, due to the increase of the fourth flow rate in embodiment 3, the working medium flow rate corresponding to the cold source flow pump 101 in the pre-cooling stage is also increased compared to embodiment 1, that is, the working medium consumption flow rate is greater than that in embodiment 1, in other words, although the diameter of the ice ball in embodiment 3 is larger, the working medium consumption flow rate is also increased.

Further, as can be seen from comparison between example 3 and example 2, increasing the flow rate (fourth flow rate) at the output side of the ablation apparatus 200 in the stage of ice ball growth has a greater influence on the diameter of the ice ball than increasing the flow rate (second flow rate) at the output side of the ablation apparatus 200 in the pre-cooling stage. That is, the flow rate (fourth flow rate) at the output side of the ablation device 200 in the stage of the growth of the ice hockey ball is increased, and the ice hockey ball with a larger diameter can be obtained.

Example 4

Embodiment 4 the thermal ablation system of fig. 1 is used, wherein the ablation device 200 is an ablation needle. The diameter of the ablation needle is the same as that of the ablation needle of example 1 described above. Except that in example 4, the opening degree of the pre-cooling phase separation valve 11 was changed, and the specific values are shown in table 4.

TABLE 4 opening degree of valve mechanism and flow data table of flow pump mechanism

In example 4, in the pre-cooling stage, the opening degree of the phase separation valve 11 is reduced on the basis of example 1, so that the first flow is reduced relative to that of example 1, and the working medium flow corresponding to the cold source flow pump 101 is increased.

However, as can be seen from table 4, the duration of the pre-cooling phase in example 4 is longer, the diameter of the ice ball obtained is smaller, and the working fluid consumption rate is also higher.

Therefore, the phase separation valve 11 is kept at a larger opening degree in the pre-cooling stage, which is beneficial to reducing the duration of the pre-cooling stage, increasing the diameter of ice balls formed in the pre-cooling stage and reducing the consumption flow of working media.

Example 5

Embodiment 5 employs the thermal ablation system of fig. 1, wherein the ablation device 200 is an ablation needle. The diameter of the ablation needle is the same as that of the ablation needle of example 1 described above. In contrast, in example 5, the opening degree of the phase separation valve 11 in the ice ball growth stage was changed, and specific numerical values are shown in table 5.

TABLE 5 opening degree of valve mechanism and flow data table of flow pump mechanism

In example 5, the opening degree of the phase separation valve 11 is reduced in comparison with example 1 in the ice ball growth stage, the third flow rate and the fourth flow rate have a small reduction tendency, and the flow rate of the working medium corresponding to the cold source flow rate pump 101 is slightly reduced in comparison with example 1.

However, as is clear from table 5, the ice ball diameter obtained in example 5 is smaller than that of example 1 and the time during which the ice ball growth stage lasts is longer.

Example 6

Example 6 the thermal ablation system of fig. 1 is used, wherein the ablation device 200 is an ablation needle. The diameter of the ablation needle is the same as that of the ablation needle of example 1 described above. Except that the opening of the fifth valve 5 in the ice hockey stabilizing stage was changed in example 6, and the specific numerical values are shown in table 5.

TABLE 6 opening degree of valve mechanism and flow data table of flow pump mechanism

In example 6, the opening degree of the fifth valve 5 in the ice ball stabilization phase is increased on the basis of example 1, so that the fifth flow rate is increased relative to the fifth flow rate in example 1, namely, in the ice ball stabilization phase, the flow rate of the working medium discharged from the output end of the ablation instrument 200 is increased compared with example 1, and as can be seen from table 6, the ice ball diameter obtained in example 6 is larger than that of example 1.

However, since the fifth flow rate in embodiment 6 is increased, the working medium flow rate corresponding to the cold source flow pump 101 is also increased compared to embodiment 1, that is, the working medium consumption flow rate is greater than that in embodiment 1, in other words, although the diameter of the ice ball in embodiment 6 is larger, the working medium consumption flow rate is also increased.

Example 7

Embodiment 7 employs the thermal ablation system of fig. 1, wherein the ablation device 200 is an ablation needle. The diameter of the ablation needle is the same as that of the ablation needle of example 1 described above. Except that the opening of the sixth valve 6 in the stable ice ball stage was changed in example 7, and the specific values are shown in table 5.

TABLE 7 opening degree of valve mechanism and flow data table of flow pump mechanism

In example 7, the opening degree of the sixth valve 6 in the puck stabilization phase is reduced based on example 1, and the sixth flow rate at this time is reduced relative to the sixth flow rate in example 1, that is, in the puck stabilization phase, the flow rate of the working medium supplemented and delivered to the ablation instrument 200 through the second storage mechanism 400 is reduced compared with example 1, so that the flow rate of the working medium corresponding to the cold source flow pump 101 is also reduced compared with example 1, that is, the working medium consumption flow rate is smaller than that of example 1.

However, as can be seen from table 7, the puck diameter obtained in example 7 is smaller than that of example 1. In other words, in example 7, although the working fluid consumption flow rate is smaller, the diameter of the obtained ice ball is also reduced.

In summary, by adjusting the opening of each valve, the working medium flow at different positions in the system can be correspondingly adjusted, so that each combination scheme of different working medium consumption flow and ice hockey size can be obtained, and the dual effects of minimum working medium consumption flow and maximum obtained ice hockey size can be obtained, so that the ice hockey control system has obvious advantages in terms of treatment effects and cost control.

When the opening degree of each valve is 100%, the valve is fully opened, and when the opening degree is 0, the valve is fully closed. While the invention has been described with reference to a preferred embodiment, various modifications may be made and equivalents may be substituted for elements thereof without departing from the scope of the invention. In particular, the technical features mentioned in the embodiments can be combined in any way as long as there is no structural conflict. It is intended that the invention not be limited to the particular embodiments disclosed, but that the invention will include all embodiments falling within the scope of the appended claims.

Claims

1. A cold and hot ablation system, comprising:

a heat sink (100), the heat sink (100) having an overall output side and a first output side connected to the overall output side thereof;

an ablation instrument (200) coupled to the cold source (100), the ablation instrument (200) having a first output side and a second output side; and

a valve mechanism for controlling the output flow of the cooling source (100) and the ablation instrument (200);

the opening degree of the valve mechanism is adjusted, so that the first output side of the cold source (100) outputs working media at a first flow rate, and the first output side of the ablation instrument (200) outputs working media at a second flow rate to pre-cool, wherein the second flow rate is greater than the first flow rate;

adjusting the opening degree of the valve mechanism to enable the first output side of the cold source (100) to output working media at a third flow rate, and the second output side of the ablation instrument (200) to output working media at a fourth flow rate, so that ice balls with a preset size are formed in the ablation instrument (200), wherein the fourth flow rate is greater than the third flow rate;

2. The system for cold and hot ablation according to claim 1, wherein the valve mechanism comprises:

a first valve (1) disposed at a general output side of the cool source (100);

a phase separation valve (11) disposed at a first output side of the cool source (100); and

a second valve (2) disposed on a first output side of the ablation instrument (200);

wherein, by controlling the opening degree of one or more of the first valve (1), the phase separation valve (11) and the second valve (2), the first output side of the cold source (100) can output working medium with a first flow rate, and the first output side of the ablation apparatus (200) can output working medium with a second flow rate.

3. A hot and cold ablation system according to claim 2, wherein the valve mechanism further comprises:

a third valve (3) arranged on a second output side of the ablation instrument (200); and

a fourth valve (4) arranged on a first supplementary tube (303) connected to a second output side of the ablation instrument (200);

wherein, by controlling the opening degree of one or more of the first valve (1), the phase separation valve (11), the second valve (2), the third valve (3) and the fourth valve (4), the first output side of the cold source (100) can output working medium with a third flow rate, and the second output side of the ablation apparatus (200) can output working medium with a fourth flow rate.

4. The system for cold and hot ablation according to claim 3, wherein the valve mechanism further comprises:

a fifth valve (5) arranged on a second supplementary tube (403) connected to the first input side of the ablation instrument (200); and

a sixth valve (6) arranged on a third output side of the ablation instrument (200);

the first input side of the ablation instrument (200) inputs treatment working medium at a fifth flow rate by adjusting the opening degree of one or more of the first valve (1), the fifth valve (5) and the sixth valve (6), and the third output side of the ablation instrument (200) outputs the treated working medium at a sixth flow rate;

wherein the sixth flow rate is greater than the fifth flow rate.

5. The system according to claim 4, further comprising a first storage mechanism (300) and a second storage mechanism (400);

the first storage mechanism (300) is respectively connected with the first output side of the cold source (100), the first output side of the ablation instrument (200) and the first supplement pipe (303), and the first storage mechanism (300) can respectively collect working media output by the first output side of the cold source (100) and the working media output by the first output side of the ablation instrument (200) or supplement working media to the second output side of the ablation instrument (200);

the second storage mechanism (400) is respectively connected with the second replenishing pipe (403) and the cold source (100).

6. The cold and heat ablation system according to any one of claims 1-3, further comprising a flow pump mechanism, the flow pump mechanism comprising:

a first flow pump (301) located at a first output side of the cold source (100) for obtaining a first flow and a third flow;

a second flow pump (302) located at a first output side of the ablation instrument (200) for obtaining the second flow;

a third flow pump (401) located at a second output side of the ablation instrument (200) for obtaining the fourth flow;

a fourth flow pump (402) on a second supplementary tube (403) connected to the first input side of the ablation instrument (200) for obtaining a fifth flow; and

a fifth flow pump (231) located at a third output side of the ablation instrument (200) for obtaining a sixth flow.

7. The cold and hot ablation system according to claim 6, characterized in that the flow pump mechanism further comprises a cold source flow pump (101) located at the general output side of the cold source (100) for obtaining a working medium consumption flow.

8. A control method of a cold and hot ablation system is characterized by comprising the following operation steps:

9. The control method of a cold and hot ablation system according to claim 8, wherein the first output side of the cooling source is controlled to output the working medium at a first flow rate by adjusting the opening degree of one or more of the first valve, the phase separation valve and the second valve, and the first output side of the ablation apparatus outputs the working medium at a second flow rate;

the phase separation valve is positioned on the first output side of the cold source;

the second valve is located on a first output side of the ablation instrument.

10. The method of controlling a cold and hot ablation system according to claim 9, wherein the first output side of the cooling source is controlled to output the working medium at a third flow rate by adjusting the opening degree of one or more of the first valve, the phase separation valve, the second valve, the third valve, and the fourth valve, and the second output side of the ablation instrument outputs the working medium at a fourth flow rate;

11. The method for controlling a thermal ablation system according to claim 10, further comprising the steps of:

ice ball stabilization stage: controlling a first input side of the ablation apparatus to input a treatment working medium at a fifth flow rate, and outputting the treated working medium at a third output side of the ablation apparatus at a sixth flow rate, so that the size of an ice ball formed in the ablation apparatus is maintained within a preset size range;

wherein the sixth flow rate is greater than the fifth flow rate.

12. The control method of a cold and hot ablation system according to claim 11, wherein the first input side of the ablation apparatus is controlled to input the treatment working medium at a fifth flow rate by making the opening degree of the phase separation valve, the second valve and the third valve zero, and the third output side of the ablation apparatus outputs the treated working medium at a sixth flow rate by adjusting the opening degree of one or more of the first valve, the fifth valve and the sixth valve;

the sixth valve is located on a third output side of the ablation instrument.